CN106535990A - Leadless pacing system including sensing extension - Google Patents

Leadless pacing system including sensing extension Download PDF

Info

Publication number
CN106535990A
CN106535990A CN201580038840.XA CN201580038840A CN106535990A CN 106535990 A CN106535990 A CN 106535990A CN 201580038840 A CN201580038840 A CN 201580038840A CN 106535990 A CN106535990 A CN 106535990A
Authority
CN
China
Prior art keywords
electrode
sensing
extension
housing
module
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
CN201580038840.XA
Other languages
Chinese (zh)
Other versions
CN106535990B (en
Inventor
T·A·安德森
T·J·谢尔顿
M·D·波纳
N·C·尼福斯
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Medtronic Inc
Original Assignee
Medtronic Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Medtronic Inc filed Critical Medtronic Inc
Publication of CN106535990A publication Critical patent/CN106535990A/en
Application granted granted Critical
Publication of CN106535990B publication Critical patent/CN106535990B/en
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/368—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
    • A61B5/283—Invasive
    • A61B5/287—Holders for multiple electrodes, e.g. electrode catheters for electrophysiological study [EPS]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/346—Analysis of electrocardiograms
    • A61B5/349—Detecting specific parameters of the electrocardiograph cycle
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/686—Permanently implanted devices, e.g. pacemakers, other stimulators, biochips
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/37205—Microstimulators, e.g. implantable through a cannula
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/375—Constructional arrangements, e.g. casings
    • A61N1/3756—Casings with electrodes thereon, e.g. leadless stimulators
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/056—Transvascular endocardial electrode systems

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Cardiology (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Veterinary Medicine (AREA)
  • Biomedical Technology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Biophysics (AREA)
  • Physiology (AREA)
  • Physics & Mathematics (AREA)
  • Pathology (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Electrotherapy Devices (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)

Abstract

A leadless pacing system includes a leadless pacing device and a sensing extension extending from a housing of the leadless pacing device. The sensing extension includes one or more electrodes with which the leadless pacing device may sense electrical cardiac activity. The one or more electrodes of the sensing extension may be carried by a self-supporting body that is configured to passively position the one or more electrodes proximate or within a chamber of the heart other than the chamber in which the LPD is implanted.

Description

Including sensing extension without lead pacing system
This application claims being submitted to and entitled " LEADLESS on July 17th, 2014 by Sheldon (Sheldon) et al. PACING SYSTEM INCLUDING SENSING EXTENSION's (include sensing extension without lead pacing system) " The rights and interests of U.S.Provisional Serial 62/025,690, the application in full combine here with which by quoting.
Technical field
It relates to cardiac pacing, and relate more specifically to using the cardiac pacing without lead pacing devices.
Background technology
Implantable pacemaker to the cardiac delivery pacemaker impulse of patient and can monitor the heart of the patient. In some examples, the implantable pacemaker includes impulse generator and one or more electrical lead.The impulse generator For example can be implanted in the tiny pocket in patient chest.The electrical lead is coupled to impulse generator, and the pulse is sent out Raw device can include the circuit for generating pacemaker impulse and/or sensing cardiac electrical activity.The electrical lead can be sent out from the pulse Raw device extends to target site (for example, atrium and/or ventricle), so that the electrode in the proximal end of electrical lead is positioned in Target site.The impulse generator can provide electro photoluminescence to the target site and/or monitor the mesh via electrode The cardiac electrical activity at mark position.
Also proposed a kind of for sensing electrical activity and/or to cardiac delivery treatment electric signal without lead pacing devices. Described one or more electrodes that can include without lead pacing devices on its housing, one or more of electrodes are used to pass Send the intrinsic depolarising for the treatment of electric signal and/or sensing heart.It is described can be positioned within heart without lead pacing devices or Outside, and can be anchored on the wall of heart via fixed mechanism in some instances.
The content of the invention
The present disclosure describes one kind is without lead pacing system, it is described to include without lead pacing devices without lead pacing system (hereinafter referred to as " LPD ") and the sensing extension extended from the housing of the LPD, wherein, the sensing extension bag One or more electrodes are included, the LPD can sense electric cardiomotility using one or more of electrodes.The sensing prolongs Extending portion is electrically coupled to the sensing module of the LPD via the current-carrying part of the housing of the LPD.The sensing extension One or more of electrodes can be carried by self-supporting body, and the self-supporting body is configured for passively will be described One or more electrodes are positioned at the heart chamber in addition to the chamber for being implanted into the LPD near or within.In some examples In, the portions of proximal of the sensing extension is configured for reducing the interference of the mechanical movement to heart.
The sensing extension promotes by the LPD to the heart chamber in addition to being implanted into the chamber of the LPD Electrical activity is sensed.The LPD is configured to be implanted in the heart chamber of patient, and the sensing extension is configured Into for extend outwardly away from the LPD so as to electrode is positioned at heart another chamber near or within, for example, for sensing State the electrical activity of another chamber.In some instances, the sensing extension includes being configured for prolonging the sensing Promote the feature of the control to the sensing extension during extending portion implantation within a patient.The feature can for example be existed The eyelet of the proximal end of the sensing extension, the eyelet is configured for being received in plants described without lead pacing system Can be used for the tether of the positioning of the near-end for controlling the sensing extension during entering in patient's body.The tether is also Can be used to confirm that the LPD is fixed to target tissue site, for example, to perform dilatory test.
On the one hand, it relates to a kind of system, the system is included without lead pacing devices, described to set without lead pace-making The standby stimulating module for including being configured for generating pacemaker impulse, sensing module, processing module, including the housing of current-carrying part And the first electrode of the sensing module and the stimulating module is electrically coupled to, wherein, the housing is configured to be implanted in In the heart chamber of patient and the fenced stimulating module, the sensing module and the processing module.The system enters one Step include sensing extension, the sensing extension extend from the housing and including：Self-supporting body, the self-supporting sheet Body extends from the housing and including the portions of proximal of bending；And second electrode, the second electrode is by the self-supporting Body is carried and the current-carrying part via the housing is electrically connected to the sensing module and the stimulating module.It is described Processing module is configured for controlling the sensing module via the second electrode to sense electric cardiomotility.
On the other hand, it relates to a kind of method, methods described includes being controlled without lead pacing devices by processor Stimulating module is to patient delivery's pacemaker impulse, described to include the stimulating module, sensing module, the place without lead pacing devices Manage device, the housing including current-carrying part and be electrically coupled to the first electrode of the sensing module and the stimulating module, wherein, The housing is configured to be implanted in the heart chamber of patient and the fenced stimulating module, the sensing module and described Processor.Methods described further include by the processor control the sensing module without lead pacing devices via The second electrode of the first electrode and the sensing extension extended from the housing is sensing electric cardiomotility, the sensing Extension further includes self-supporting body and the second electrode, the self-supporting body extend from the housing and including The portions of proximal of bending, the second electrode are carried by the self-supporting body and via the current-carrying part of the housing It is electrically connected to the sensing module and the stimulating module.
On the other hand, it relates to a kind of system, the system includes：It is without lead pacing devices, described to rise without lead The equipment of fighting include being configured for generating the stimulating module of pacemaker impulse, sensing module, processing module, including current-carrying part Housing and the first electrode of the sensing module and the stimulating module is electrically coupled to, wherein, the housing is configured to plant Enter in the heart chamber of patient and the fenced stimulating module, the sensing module and the processing module, and wherein, The current-carrying part is electrically connected to the sensing module.The system further includes to sense extension, the sensing extension Extend from the housing and including：Self-supporting body, be connected to the self-supporting bulk mechanical the housing and including It is electrically connected to the conductor of the current-carrying part of the housing；Second electrode, the second electrode are held by the self-supporting body Carry and be electrically connected to the conductor；And in the eyelet of the proximal end of the sensing extension.
On the other hand, it relates to a kind of system, the system is included without lead pacing devices, described to pace without lead Equipment includes being configured for generating the stimulating module of pacemaker impulse, sensing module, processing module, is configured to be implanted in trouble Housing in the heart chamber of person and the first electrode of the sensing module and the stimulating module is electrically coupled to, wherein, institute State the fenced stimulating module of housing, the sensing module and the processing module.The system further includes extension, institute State extension extend from the housing and including：Body, is connected to the housing and including being electrically connected the bulk mechanical It is connected to the conductor of at least one of the sensing module or the stimulating module；Second electrode, the second electrode is by described Body is carried and is electrically connected to the conductor；And in the eyelet of the proximal end of the extension.
On the other hand, it relates to a kind of method, methods described includes being controlled without lead pacing devices by processor Stimulating module is to patient delivery's pacemaker impulse, described to include the stimulating module, sensing module, the place without lead pacing devices Reason device, it is configured to the housing that is implanted in the heart chamber of patient and is electrically coupled to the sensing module and the stimulation mould The first electrode of block, wherein, the fenced stimulating module of the housing, the sensing module and the processing module.The side Method further includes to control the sensing module without lead pacing devices via the first electrode by the processor And the second electrode of the sensing extension extended from the housing, sensing electric cardiomotility, the sensing extension is further Including：Body, is connected to the housing and including the conductor for being electrically connected to the sensing module bulk mechanical；Second Electrode, the second electrode are carried by the body and are electrically connected to the conductor；And the proximal end of the extension Eyelet.
On the other hand, it relates to a kind of computer-readable recording medium, which includes can be by the calculating of computing device Machine readable instruction.The instruction causes programmable processor to perform any all or part of technology described here.The finger Order can be, for example, software instruction, such as limiting those instructions of software or computer program.Computer-readable medium Can be computer-readable recording medium, such as storage device (for example, disc driver or optical drive), memory (example Such as, flash memory, read-only storage (ROM), or random access memory (RAM)) or store instruction (for example, with computer program or Other executable forms) with cause programmable processor perform any other type of technology described here volatibility or Nonvolatile memory.In some instances, the computer-readable medium is a kind of product and is non-transient.
The details of one or more examples is elaborated in the following drawings and description.By the specification and drawings and right Claim, other features, purpose and advantage will be apparent from.
Description of the drawings
Fig. 1 is illustrated including the example without lead pacing devices and sensing extension without lead pacing system.
Fig. 2 is the schematic cross-sectional view of the sensing extension of Fig. 1.
Fig. 3 is the conceptual representation without lead pacing system being implanted in patient's body of Fig. 1.
Fig. 4 A to Fig. 4 C illustrate the example shapes of the near-end of sensing extension.
Fig. 5 is illustrated including another example without lead pacing devices and sensing extension without lead pacing system.
Fig. 6 is the schematic cross-sectional view of the sensing extension of Fig. 5.
Fig. 7 is the perspective view that another example senses extension.
Fig. 8 is the perspective cross-sectional view of the sensing extension of Fig. 7.
Fig. 9 is the decomposition diagram of the sensing extension of Fig. 7.
Figure 10 is functional block diagram of the example without lead pacing system.
Figure 11 be it is a kind of for using Fig. 1 without lead pacing system delivering the example treated and sense electric cardiomotility The flow chart of technology.
Specific embodiment
It is a kind of to include LPD and sensing extension without lead pacing system, the sensing extension be coupled to the LPD and It is configured for promoting to sense the electrical activity of the heart chamber in addition to being implanted into the chamber of the LPD.The sense Survey the self-supporting body that extension includes one or more electrodes and extends away from the shell of the LPD.With with lead Pacing system is compared, the lead for not including from heart passing without lead pacing system described here.Conversely, LPD and sensing prolong Extending portion both of which is configured for being fully implanted in the heart of patient.In some instances, sense the size quilt of extension Be arranged to be fully implanted in in LPD identical heart chambers.In other examples, LPD is configured to be implanted in heart In one chamber, and sense extension be configured and dimensioned to extend into another chamber.
LPD is configured to be implanted in the first chamber (for example, ventricle) of patient's heart, and senses extension and be configured Into the second chamber for one or more electrodes to be positioned at heart near or within, for example, for sensing second chamber Electrical activity.Sensing extension has enough length to orientate one or more electrodes of sensing extension as appointing than LPD What electrode is closer to second chamber.For example, when LPD is implanted in the apex of the heart of right ventricle or nearby, the sensing extension can To close on atrium dextrum or be positioned at the right heart with being selected for orientating one or more of electrodes of sensing extension as Length in room.One or more of electrodes of sensing extension can be used for sensing intrinsic ventricle electrical activity and detecting Atrial electrical activity.
In some examples described here, self-supporting body is configured for passively (fixing without the need for any active Element (such as prong or fixed spiral)) electrode extension is remotely located from the position of LPD, for example, near heart At the position of second chamber.When self-supporting body contacts are organized, the body can enough flexibly to reduce to heart group The stimulation knitted, but with enough rigidity so as to allow sense extension extend outwardly away from LPD housings and towards second chamber (i.e. In the case of making to there is blood in the first chamber of heart).The rigidity of self-supporting body is selected to help prevent State body on itself and/or (for example, in the case where there is blood flow) is subsided towards LPD.Furthermore, it is possible to self-supporting sheet The rigidity of body is selected, so that the body is configured for supporting the weight of its own (for example, there is gravity In the case of).
Sensing extension also includes the portions of proximal of the interference for being configured for helping reduce the mechanical movement to heart. For example, it is configured to be implanted in the ventricle of heart and sense extension in LPD and is configured for extending towards atrium In example, the shapes and sizes for sensing the portions of proximal of extension can be arranged for reducing to atrioventricular valve (for example, tricuspid Lobe or bicuspid valve) opening and closure interference.Additionally, the near-end of sensing extension is configured to noninvasive (for example, blunt), If the stimulation to heart tissue is reduced when being contacted with heart tissue so as to near-end.As can help reduce to heart The example of the configuration of the portions of proximal of the interference of mechanical movement, portions of proximal can bend one or more turn of bilges.For example, closely Side part can limit L-shaped curve, C-shaped curve, pigtail shape or any other suitable curve.
In some instances, sensing extension also includes being configured in by the sensing extension implantation heart During promote to it is described sensing extension control feature.In these examples, sensing extension may or may not With self-supporting body.In some instances, the feature is included in the eyelet of the proximal end of sensing extension.Tether can be It is fed by the eyelet before the heart that LPD and sensing extension are introduced patient.In implantation process, clinician can Help control the position of the near-end for sensing extension to retract the tether, so as to confirm that LPD is properly fixed mesh Mark tissue site (for example, confirm LPD not in response to the pulling to tether movement " dilatory test ").After the implants, Tether can be removed from eyelet.
Fig. 1 is conceptual representation of the example without lead pacing system 10 for including LPD 12 and sensing extension 14.LPD 12 Be configured to be implanted in the heart chamber of patient, for example, control for monitoring the electrical activity of heart and/or electricity being provided to heart Treat.In the example shown in fig. 1, LPD 12 includes shell 16, multiple fixing tooths 18, and electrode 20.Sensing extension 14 is wrapped Include self-supporting body 22, electrode 24 and conductor 26.
Shell 16 has allows LPD 12 to be fully implanted in the size and shape factor in the heart chamber of patient.At some In example, shell 16 can have cylinder (for example, pill shape) form factor.LPD 12 can include being configured for LPD 12 is fixed to into the fixed mechanism of heart tissue.For example, in the example shown in fig. 1, LPD 12 includes fixing tooth 18, institute State it is that fixing tooth extends from housing 16 and be configured for engaging with heart tissue so as to by the position of housing 16 substantially It is fixed on the within the chamber of heart.Fixing tooth 18 is configured for housing 16 being anchored in heart tissue, so that LPD 12 move along heart tissue in systole.Fixing tooth 18 can be made up of any suitable material, such as shape Memory material (for example, Nitinol).Although LPD 12 includes being configured for LPD 12 is anchored to the heart in heart chamber Dirty structural multiple fixing tooths 18, but in other examples, LPD 12 can using other kinds of fixed mechanism (such as but It is not limited to barb, coil etc.) and it is fixed to heart tissue.
Housing 16 accommodates the electronic unit of LPD 12, for example, for the sensing of cardiac electrical activity is sensed via electrode 20,24 Module and the electrical stimulation module for electronic stimulation is delivered via electrode 20,24.Electronic unit can include any discrete And/or integrated electronic circuit part, the part realizes the simulation that can produce the function of being attributed to LPD described here 12 Circuit and/or digital circuit.In some instances, housing 16 can also be accommodated and (such as be accelerated for sensing other physiological parameters Degree, pressure, sound, and/or impedance) part.
In addition, housing 16 can also accommodate the memory including instruction, the instruction is when by be contained in housing 16 LPD 12 is caused to perform the various functions for being attributed to LPD12 in this during individual or multiple computing devices.In some instances, shell Body 16 can accommodate the communication mould that LPD 12 is communicated with other electronic equipments (such as medical device programmer) Block.In some instances, housing 16 can accommodate the antenna for radio communication.Housing 16 can also accommodate power supply, such as electricity Pond.Housing 16 can be it is gas-tight seal or be close to it is gas-tight seal, to help prevent fluid to import in housing 16.
LPD 12 is configured for sensing the electrical activity of heart and via electrode 20,24 to cardiac delivery electro photoluminescence. LPD 12 includes electrode 20, and senses extension 14 and include electrode 24.For example, electrode 20 can be mechanically connected to housing 16.Used as another example, electrode 20 can be limited by the conductive external part of housing 16.Fixing tooth 18 is configured for LPD 12 is anchored in heart tissue, so that electrode 20 keeps the contact with heart tissue.
Sensing extension 14 be configured for by electrode 24 be positioned at the chamber of implantation LPD 12 nearby or outside.Example Such as, sense extension 14 to be configured for for electrode 24 being positioned at the chamber in addition to the be resident chambers of LPD 12 It is interior.In this mode, sensing extension 24 can be with the sensing function of stretch system 10.In the example shown in fig. 1, electrode 24 is by feeling The self-supporting body 22 for surveying extension 14 is carried and positioned at the proximal end of body 22.However, in other examples, electrode 24 can With with the another location relative to body 22, such as at the intermediate range between the near-end of housing 16 and body 22, or with its other party Near-end of the formula away from body 22.Electrode 24 can have any suitable configuration.For example, electrode 24 can have loop configurations, Or part-toroidal configuration.Electrode 24 can be formed by any suitable material, such as titanium nitride coating metal.
In other examples, system 10 can include more than two electrode.For example, LPD 12 and/or sensing extension 14 There can be more than one electrode.As an example, with can be by with one or more supplemantary electrodes of 24 identical polar of electrode Sensing extension 14 is carried.One or more of supplemantary electrodes can be electrically connected to identical or different with sensing extension 14 Electric conductor.The supplemantary electrode of sensing extension 14 can increase the electrode of system 10 and be oriented to for except implantation The possibility sensed by the electrical activity of the heart chamber outside the chamber of LPD 12.
In the example shown in fig. 1, current-carrying part of the electrode 24 via the electric conductor 26 and housing 16 of sensing extension 14 16A is electrically connected at least some electronic device (for example, sensing module and stimulating module) of LPD 12.Electric conductor 26 is electrically connected to The current-carrying part 16A and electrode 24 of housing 16 and the extension between the current-carrying part and electrode of housing.Current-carrying part 16A and electricity Pole 20 electrically insulates but is electrically connected to electrode 24, so that current-carrying part 16A and electrode 24 have identical polarity and electrically Common (electrically common).For example, electrode 20 can be carried by the Part II 16B of housing 16, described second Divide and electrically insulate with current-carrying part 16A.The current-carrying part 16A of housing 16 is electrically connected at least some electronic device (example of LPD12 Such as, sensing module, electrical stimulation module, or both), so that current-carrying part 16A limit from electrode 24 to the electronic device Conductive path a part.In some instances, current-carrying part 16A can limit at least of the power supply shell of LPD 12 Point.The power supply shell can accommodate the power supply (for example, battery) of LPD 12.
In some instances, current-carrying part 16A is substantially completely electrically insulated and (for example, is electrically insulated completely or almost complete Electric insulation).The current-carrying part 16A being substantially completely electrically insulated can help the sensing module of LPD12 using sensing extension 14 Electrode 24 sensing electric cardiomotility.For example, in the example that LPD12 and sensing extension are implanted in right ventricle, such as close Illustrate and describe in Fig. 3, the current-carrying part 16A being substantially completely electrically insulated can help electrode 24 to extract higher far field P Ripple.However, in other examples, at least a portion of current-carrying part 16A can be exposed for limiting one or more electrodes, The electrode with 24 identical polarity of electrode.
Such as Fig. 2, (which is that the schematic cross-section of the part for the current-carrying part 16A for sensing extension 14 and housing 16 is regarded Figure) shown in, in some instances, conductor 26 can be coiled to set up conductor 26 and current-carrying part 16A around current-carrying part 16A Between electrical connection.However, in other examples, it is possible to use another kind of configuration come set up conductor 26 and current-carrying part 16A it Between electrical connection.For example, conductor 26 can not be coiled in sensing extension 14 and can crimp or otherwise by It is positioned to contact with the current-carrying part 16A of the distal end 14A annexes of sensing extension 14.
The example that Fig. 2 is also illustrated between electrode 24 and conductor 26 is electrically connected.Specifically, Fig. 2 illustrates the near of conductor 26 Side part is soldered to the example of the distal part of electrode 24, and the distal part includes distal end 24A.In other examples, electricity Pole 24 and conductor 26 can be electrically connected using another kind of configuration.As shown in Fig. 2 in some instances, electrode 24 can be Proximal end is substantially closed, and this can help prevent fluid, and into the interior section for sensing extension 14, (for example, conductor 26 is determined Where position).
In the example shown in Fig. 1 and Fig. 2, the self-supporting body 22 of sensing extension 14 is between housing 16 and electrode 24 Extend.Self-supporting body 22 have allow body 22 be kept substantially (for example, completely keep or be close to keep) its relative to The position of LPD 12 or at least relative to LPD 12 electrode 24 position rigidity (even if there is gravity and in the heart In the case of there is blood flow in dirty).For example, self-supporting body 22 can be with about 0.8e-6N-m2To about 4.8e-6N-m2 (about 0.8 × 10-6To about 4.8 × 10-6N-m2) bending stiffness, such as about 1.6 newton square metre (N-m2).At other In example, the self-supporter with other bend stiffness can also be used.
Self-supporting body 22 is configured for passively being remotely located from the position of LPD 12, for example electrode 24, Heart chamber in addition to being implanted into the chamber of LPD 12 is near or within.For example, self-supporting body 22 can have enough Rigidity (for example, rigidity) extend outwardly away from housing 16 to allow to sense extension 14, or even when sensing extension is in cardiac chambers When moving in the blood in room.Additionally, self-supporting body 22 can enough flexibly to minimize the stimulation of the tissue to heart (in the case of 22 contact tissue of body).
In some instances, the bending stiffness through the length self-supporting body of self-supporting body 22 is substantially identical (for example, from the distal-to-proximal identical or close of body 22).In other examples, self-supporting body 22 can be along its length With stiffness variable.For example, self-supporting body can reduce rigidity from distal end (closest to the housing 16 of LPD 12) to near-end, from And allow with the distal part of 16 immediate body 22 of housing with than body 22 closest to electrode 24 and including The higher rigidity of the portions of proximal of near-end.For example, distal part can be configured with highest rigidity, and portions of proximal It is configured with minimum rigidity.The more Low rigidity of the proximal portion of body 22 can help be further minimized to heart Tissue stimulation (body 22 proximal contact organize in the case of), and harder distal part can allow body 22 will Electrode 24 is remotely located from the position of LPD 12.
In the example shown in Fig. 1 and Fig. 2, electric conductor 26 is by conductions such as such as polymer (for example, polyurethane) or silicone Body material is covered.For example, as depicted in figs. 1 and 2, conductor 26 can be contained in polyurethane or silicone sleeve 28.In some feelings Under condition, coil type conductor 26 can not provide enough rigidity so that self-supporting body 22 being capable of base to sensing extension 14 Which is kept in sheet relative to the position (in the case of there is blood flow in heart) of LPD12.Thus, in some instances, sense Extension 14 can also include rigid member 30, and the rigid member is with higher than coil type conductor 26 (when coiling) firm Degree.In the example shown in Fig. 1 and Fig. 2, the self-supporting body 22 of extension 14 is sensed by conductor 26, sleeve pipe 28 and rigid member 30 limit.
Rigid member 30 has the rigidity for helping prevent self-supporting body 22 to subside on itself and/or towards LPD 12 (such as in the case of there is blood flow).For example, the example in polyurethane or silicone sleeve is coiled and is enclosed in conductor 26 In, rigid member 30 can have rigidity to cause self-supporting body 22 with about 0.8e-6N-m2To about 4.8e-6N-m2 (about 0.8 × 10-6To about 4.8 × 10-6N-m2) rigidity.However, it is possible to suitable for providing institute's phase to self-supporting body 22 The rigidity of the rigid member 30 of the stiffness characteristics of prestige is likely to be dependent on various factors, such as the length of self-supporting body 22 and from Support body 22 diameter (or when cross section be considered as when being substantially perpendicular to longitudinal axis self-supporting body 22 have not rounded Other cross sectional dimensions in the example of shape shape of cross section).Rigid member 30 can be with the length of self-supporting body 22 Increase and harder with the increase of the diameter of self-supporting body.Bigger diameter can cause blood flow by the self-supporting of surrounding Body 22 is more pushed in heart.As self-supporting body 22, in some instances, rigid member 30 can be with along which Length has stiffness variable or can have substantially the same rigidity along its length.
Rigid member 30 can be nonmetallic by any suitable material or metal material is formed, and such as nickel-cobalt-chromium-molybdenum is closed Golden (for example, MP35N, such as 7 × 7MP35N cable).
Additionally, rigid member 30 can be executed for confirm LPD 12 be fixed to target tissue site (for example, that A little teeth 18 are fixedly engaged with the tissue of the heart of patient) dilatory test process in response to being applied to sensing extension 14 Near-end (end furthest away with LPD 12) pulling force and limit sensing extension 14 stretch amount.It is (all in some examples As in the example that conductor 26 is coiled) in, conductor 26 can be stretched in response to pulling force (for example, elongate).However, showing at some In example, rigid member 30 is with may be configured to stretching, extension little than conductor 26, and as a result, when clinician is being used to confirm LPD 12 be fixed in the dilatory test process of target tissue site by pulling force be applied to sensing extension 14 near-end (with End LPD 12 furthest away) when, rigid member 30 can be in response to not including rigid member relative to sensing extension 14 The pulling force of 30 example and limit sensing extension 14 stretch amount.
As depicted in figs. 1 and 2, in some instances, (for example, conductor 26 can by coil type conductor 26 for rigid member 30 To coil around component 30) center extend and the longitudinal axis with sensing extension 14.However, in other examples, just Property component 30 can have another location in sensing extension 14.
In other examples (such as in the example that conductor 26 is not coiled), sensing extension 14 can not include rigidity Component 30.For example, the material of sleeve pipe 28 is combined with conductor 26 and can be provided enough rigidity to allow body 22 for body 22 Which is kept relative to the position (in the case where there is gravity and there is blood flow in heart) of LPD 12.
In some instances, except or replace electrode 24 is electrically connected to the electronics device of LPD 12 via electric conductor 26 Part, rigidity member 30 can be electronic devices conductive and that electrode 24 can be electrically connected to LPD 12.For example, rigidity structure The portions of proximal of part 30 can be soldered or otherwise be electrically connected to the distal part of electrode 24.Thus, show at some In example, sensing extension 14 does not include electric conductor 26, and electrode 24 both can be electrically connected to LPD's 12 by rigid member 30 Electronic device can increase the rigidity of sensing extension 14 again, for example, to help prevent self-supporting body 22 on itself And/or subside towards LPD 12.Rigid member 30 can have the ratio such as higher rigidity of sleeve pipe 28.In electric conductor 26 and rigidity In the example of the electronic device that electrode 24 is electrically connected to both components 30 LPD 12, sensing extension 14 can be provided for inciting somebody to action Electrode 24 is electrically connected to the redundancy electric pathway of the electronic device of LPD 12.
In the example shown in Fig. 1 and Fig. 2, system 10 includes the far-end or neighbouring receipts for being positioned at sensing extension 14 Component 31 is returned, it is described to withdraw the shell 16 that component is mechanically connected to LPD 12.Withdraw component 31 to may, for example, be projection, dash forward Rise or can be used for for example when remove in patient's body or during implant system 10 grasping system 10 any other suitable spy Levy.For example, withdraw component 31 and can be arranged to the projection for being captured by snare.In some instances, withdraw component 31 are bonded to for isolating in the molding part for sensing extension 14, or can be integrally formed with shell 16.Show at other In example, withdraw component 31 and can separate with sensing extension 14, shell 16 or both or be attached to the sensing extension, shell Or both.
As discussed above, sense extension 14 to be configured for electrode 24 is positioned at the chamber except being implanted into LPD 12 Outside heart chamber near or within.Fig. 3 illustrates the system 10 in the right ventricle 32 of the heart 34 for being implanted in patient 36. In example shown in Fig. 3, sensing extension 14 is configured for the time delay in LPD 12 is implanted in the apex of the heart of right ventricle 32 Stretch away from LPD 12 and towards atrium dextrum 38.In some instances, as shown in figure 3, sensing extension 14 can have permission Sensing extension 14 stills remain in the length in the right ventricle 32 with LPD 12.For example, sense extension 14 to have The length of about 40 millimeters (mm) to about 150mm, such as about 60 millimeters (such as from the distal end and electrode 24 for being connected to LPD 12 Proximal measurement).Single chamber system 10 can provide sensing two chambers (for example, the right ventricle 32 in the example shown in Fig. 3 With the advantage of atrium dextrum electrical activity 38), without extension 14 is placed on the burden in atrium dextrum 38.
Still remain in the example in 12 identical chambers of LPD in extension 14, sense the proximal portion of extension 14 Point be configured for helping reducing the mechanical movement to heart interference (such as in the example shown in Fig. 3, tricuspid valve Motion).For example, as shown in respectively about electrode 25A, 25B and the 25C in Fig. 4 A, Fig. 4 B and Fig. 4 C, extension 14 The electrode 24 of proximal end defines L-shaped curve, C-shaped curve, pigtail shape or any other suitable curve.L is also show in Fig. 3 Shape curve.
L-shaped curve, C-shaped curve and pigtail shape curve shown in Fig. 4 A, Fig. 4 B and Fig. 4 C can limit tricuspid valve (or Person for LPD 12 other implant sites in the case of other lobes) can be still substantially proximate to it bending or phase To flat surfaces (for example, surface 27A-27C), this can help prevent blood to flow back into another chamber of heart 34 (for example, Atrium dextrum 38) in.In some instances, can select to sense the portions of proximal of extension 14 based on the implantation position of system 10 Shape.Different shapes can help reduce different valves and different implant sites to LPD 12 and sensing extension 14 Interference.
In other examples, in addition to electrode 24 or the electrode, sensing a part of of extension 14 can limit The shape illustrated in Fig. 4 A to Fig. 4 C.For example, sleeve pipe 28 and rigid member 30 are configured for limiting Fig. 4 A extremely The portions of proximal shape illustrated in Fig. 4 C, and electrode 24 can be positioned on the outer surface of sleeve pipe 28.
In other examples, sense extension 14 can with when LPD 12 is implanted in the apex of the heart of right ventricle 32 at least So that electrode 24 extends to the length in atrium dextrum 38.Extend in the example in atrium dextrum 38 in sensing extension 14, sense Extension 14 can with it is relatively small and enough flexibly so as to allow tricuspid valve sensing extension 14 around it is close enough, so as to Prevent from flowing back into atrium dextrum 38 from right ventricle 32.For example, sense extension 14 diameter can be about 4Fr (i.e. about 1.33 millimeter).
LPD 12 can sense the electrical activity of atrium dextrum 38 or right ventricle 32 using electrode 20,24.As shown in figure 3, sense Extension 14 is passive and extends outwardly away from LPD 12 for survey, and this causes electrode 24 to be relatively close to atrium dextrum 38 and be positioned.Electricity The distance between pole 24 and atrium dextrum 38 can be less than the distance between the electrode 20 of LPD12 and atrium dextrum 38.As a result, electric Pole 24 can be positioned such that the P ripples extracted than the more high amplitude of electrode 20.In this way, sensing extension 14 can be in LPD 12 Promote atrial sense when in implantation right ventricle 32.
Be attached to heart tissue so that electrode 24 with 34 directly contact of heart conversely, the nearside of sensing extension 14 Part is passive, so that sensing extension 14 can be moved in right ventricle 32.However, at least partially due to body The self-supporting configuration of 22 (Fig. 1 and Fig. 2), sensing extension 14 are configured to continue to extend outwardly away from LPD 12 and towards atrium dextrum 38 (even if existing from atrium dextrum 38 in the case of the blood flow of right ventricle 32).To sense the self-supporting construction element 22 of extension 14 Some flexibilities are provided can enable to sense extension 14 and minimize and right ventricle 32 (or is implanted in LPD 12 another Another chamber in the case of in chamber) in blood flow interference.
It is also shown that medical device programmer 40 in Fig. 3, the medical device programmer is configured for LPD 12 are programmed and retrieve data from LPD 12.Programmable device 40 can be Handheld computing device, desk-top computing device, networking Computing device etc..The computer-readable recording medium with instruction can be included in, programmable device 40, the instruction causes programmable device 40 processor provides the function of the programmable device 40 being attributed in the disclosure.LPD 12 can carry out channel radio with programmable device 40 Letter.For example, LPD 12 can transmit data and can be from 40 receiving data of programmable device to programmable device 40.Programmable device 40 can be with Wireless programming and/or wireless charging are carried out to LPD 12.
The electricity of the instruction heart 34 that can include being stored by LPD 12 from the data that LPD 12 is retrieved using programmable device 40 The generation and timing of sensed event, diagnostic event and treatment event that the heart EGM of activity and instruction are associated with LPD 12 Mark channel data.Use programmable device 40 include for example causing LPD 12 as described herein to the data that LPD 12 is transmitted As the operation sequence of LPD 12 that operated.
By using any suitable technology, right ventricle 32, or heart 34 can be implanted in without lead pacing system 10 In another chamber.In some cases, during sensing extension 14 can be included in and system 10 is implanted in 36 body of patient Help controls the feature of the position of the near-end for sensing extension 14.The feature can be also used for promoting for example moving system 10 The near-end of sensing extension 14 is captured during planting in 36 body of patient by withdrawal equipment relatively easily.Fig. 5 and Fig. 6 shows The example of this feature.
Fig. 5 and Fig. 6 illustrate the example without lead pacing system 50, described without lead pacing system similar to Fig. 1 to be System 10 but further include sensing extension 14 proximal end eyelet 52.However, in other examples of system 50, sensing Extension can be any suitable extension, for example, can not include that self-supporting body (is such as described above with respect to Fig. 1 and Fig. 2 ), one or more supplemantary electrodes (one or more of supplemantary electrodes can be used for sensing or electro photoluminescence) can be included, or Its any combinations.
Eyelet 52 defines and is configured for receiving for example being implanted into, transplants out, or implantation and transplanting out both mistakes The opening 54 of tether or another instrument used in journey.With sensing extension 14 compared with, tether may, for example, be suture or Person's relatively thin and flexible another kind material.The tether can pass through opening by loopback before system 10 is inserted right ventricle 32 54, and after sensing extension 14 is implanted in heart 34 (Fig. 3), clinician can retract the tether to retract Sensing extension 14 near-end 14B, so as to moving sensing extension 14 near-end 14B or otherwise control near-end 14B Position.Additionally, eyelet 52 be configured for promote for example during system 10 is transplanted out in patient's body by Withdrawal equipment carrys out capture systems 10, or for LPD 12 is moved to another one after being already affixed to ad-hoc location in tooth 18 Put.
Although being shown as with circular cross section in fig. 5 and fig., eyelet 52 can have and be configured for connecing Receive any suitable shape of cross section of tether or other instruments.In addition, although be shown as limiting in fig. 5 and fig. Opening, the opening is with horizontal and substantially orthogonal with the longitudinal axis 15 of sensing extension 14 (for example, orthogonal or connect It is near orthogonal)) central axis 53, but in other examples, central axis 53 can be with another court relative to longitudinal axis 15 To.For example, the opening for being limited by eyelet 52 may be oriented so that central axis 53 it is substantially parallel (for example it is, parallel or It is close to parallel) or be directed with the angle less than 90 degree relative to longitudinal axis 15.Thus, in some instances, by eyelet 52 The opening of restriction may be oriented so that central axis 53 is 90 degree or less relative to longitudinal axis 15.
Additionally, in some instances, central axis 53 can not be aligned with longitudinal axis 53, but eyelet 52 can extend far From the side surface of extension 14.In fig. 5 and fig., central axis 53 is aligned with longitudinal axis 53.If however, for example sensing prolongs Extending portion 14 defines the portions of proximal (for example, as shown in Fig. 4 A to Fig. 4 C) of bending, then central axis 53 can not be with longitudinal axis 53 alignments.
Eyelet 52 can be mechanically connected to sensing extension 14 using any suitable technology.Shown in Fig. 5 and Fig. 6 In example, eyelet 52 includes the base portion 56 being contained in the cavity 58 limited by electrode 24.Any suitable technology can be used Come adhesive electrodes 24 and base portion 56, such as by via adhesive, welding, or another kind of technology being adapted to electrode 24 is crimped onto On base portion 56.Sense the attachment between extension 14 and eyelet 52 sufficiently strong to keep between eyelet 52 and sensing extension 14 Mechanical connection (even if exist away from sensing extension 14 side pull up eyelet 52 power (for example, from tether or its His retrieving tool) in the case of).Similarly, the attachment between LPD 12 and sensing extension 14 is sufficiently strong to keep LPD Mechanical connection between 12 and sensing extension 14 is (even if exist pull sensing extension 14 and LPD 12 power away from each other In the case of).
In some instances, the end 58A of cavity 58 can be closing (i.e. cavity 58 can be blind hole), and this can help The thing that prevents the pollution of the environment is introduced in the part including conductor 26 of sensing extension 14.
Eyelet 52 can be formed by any suitable material.In some instances, eyelet 52 is formed by non-conducting material. In other examples, eyelet 52 is formed by conductive material.In some examples that eyelet 52 is formed by conductive material, eyelet is configured Into the extension as electrode 24.Thus, LPD 12 can be sensed electric heart signal and deliver electro photoluminescence by means of eyelet 52. Eyelet 52 can be electrically connected to electrode 24 by contacting with electrode 24.In other examples that eyelet 52 is formed by conductive material In, when compared with the electric conductivity of electrode 24, the electric conductivity of eyelet 52 can be with relatively low, so that eyelet 52 serves as electrode 24 Extension.For example, eyelet 52 can be formed by stainless steel.Additionally, when system 10 is implanted in patient's body, eyelet 52 is configured Cheng Buyu heart tissues are contacted, and for example, sensing extension is configured for being positioned to not contact with heart tissue by eyelet, from And allow eyelet 52 to be not used as stimulating electrode.
The base portion 56 of eyelet 52 is shown as the axis coaxial with sensing extension 14 in fig. 5 and fig., shows at some In example, base portion 56 can have another kind of arrangement relative to the longitudinal axis of sensing extension 14.For example, in the nearside of extension 14 Part is defined to curve in the example of (for example, as shown in Fig. 4 A to Fig. 4 C), when eyelet 52 is positioned in sensing extension During 14 proximal end, base portion 56 can be bent with portions of proximal.Used as another example, base portion 56 can be curve or its other party Formula nonlinear (an angle of 90 degrees can be limited for example) and be attached to sensing extension 14 so that base portion 56 is extended outwardly away from Electrode 24.The eyelet 52 of other configurations can also be used.
Eyelet 52 provides the feature of the positioning for being used to controlling extension 52 and promotes system 50 is received from implant site The feature returned.These features may can be used for electronic device (for example, stimulating module, sensing module or two for being connected to LPD 12 Person) other kinds of extension.Thus, in some instances, system 50 can be included with different from sensing extension 14 The extension of configuration, the extension are included in the eyelet 52 of proximal end.For example, in fig. 5 and fig., be connected to sensing and prolong Extending portion 14 (the sensing extension includes the electrode 24 of the current-carrying part 16A of the housing 16 for being electrically connected to LPD 12) different, LPD 12 extensions that can be mechanically connected to the multiple electrodes including the current-carrying part 16A for being electrically connected to housing 16, and it is described Extension can extend outwardly away from the housing 16 of LPD 12 and be included in the eyelet at near-end (position similar to illustrating in Fig. 5) place 52。
Used as another example, LPD 12 can be mechanically connected to including the current-carrying part 16A for being not electrically connected to housing 16 But electronic device (the example of LPD 12 is connected to using another conductive path (conducting feed throughs for such as extending by housing 16) Such as, sensing module and stimulating module) one or more electrodes extension；In this example, eyelet 52 can be positioned at institute The proximal end of extension is stated, the extension can also extend outwardly away from housing 16.Used as still another example, LPD 12 can be with machine Be connected to is not self-supporting and/or the extension including one or more retaining elements tool.In these examples, eyelet 52 can To be positioned at the proximal end of the extension.It is also contemplated that the extension of other configurations including eyelet 52.
In other examples of system 50, sensing electrode 24 and eyelet 52 can be integrated in it is common, in unitary members. Fig. 7 to Fig. 9 illustrates the example of this sensing extension.Fig. 7 is the perspective view that example senses extension 60, the sensing extension Portion can be similar to the sensing extension 14 of Fig. 5 and Fig. 6, but non-sensing is electric including restriction electrode part 64 and eye portion 66 The sensing electrode 62 of pole 24 and eyelet 52.Fig. 8 is the perspective cross-sectional view for sensing extension 60, and illustrates self-supporting body 22nd, electric conductor 26, rigid member 30, and sensing electrode 62.Fig. 9 is the decomposition diagram for sensing extension 60.
As shown in Figure 7 to 9, electrode part 64 and eye portion 66 are continuous, and are the common of sensing electrode 62 The some of body, rather than the separate part being attached together.Comparatively speaking, the sensing electrode for illustrating in fig. 5 and fig. 24 and eyelet 52 be separate part.Eye portion 66 is configured similarly to eyelet 52 and defines be configured for receiving For example being implanted into, transplant out, or implantation and the tether used during transplanting out both or another instrument opening 68.
Including integral electrode part 64 and eye portion 66 electrode 62 can minimize liquid can by its entrance The quantity of the opening of the interior section (for example where, conductor 26 is positioned) of sensing extension 60.
Electrode 62 can be formed using any suitable technology.In some instances, it is possible to use cold-heading operation is producing Metal or other suitable conductive materials are defined to the shape of electrode 62 for electrode 62, the cold-heading operation.In some instances, After the shape for forming electrode 62, eye portion 66 can be polished.A completely or only part for electrode 62 can be Conductive.For example, in some instances, electrode part 64 and eye portion 66 are conductive (although they may have not Same impedance), and in other examples, eye portion 66 is nonconducting and electrode part 64 is conductive.Show at some Example in, in order to form the electrode 62 including nonconducting eye portion 66, can with conductive material (titanium nitride (TiN)) to electricity Eye portion 66 is sheltered during being coated pole part 62.
As electrode 24, sensing electrode 62 (such as can be retouched above with respect to electrode 24 using any suitable technology Those stated) be electrically connected to electric conductor 26, rigid member 30, or rigid member 30 and electric conductor 26 both.For example, conductor 26 or The portions of proximal of rigid member 30 can be soldered or crimp to the distal part of electrode 62.
Electrode 62 can limit distal part 62A for being configured for being contained in self-supporting body 22.Additionally, one In a little examples, as shown in figure 9, distal part 62A can limit the opening for being configured for receiving rigid member 30, so that Rigid member 30 and electrode 60 partly co-extensive, for example overlap in a longitudinal direction.However, in other examples, just Property component 30 and electrode 60 can not be co-extensive.Electrode 60 for example can provide enough to the near-end of sensing extension 60 Rigidity, and without the need for rigid member 30.
Electrode 62 (such as can be received in self-supporting by distal part 62A of electrode 62 using any suitable technology Realized when in the near-end 22B of body 22 friction fitting, by ultra-sonic welded, by adhesive or any other be adapted to Technology or the technology combination) be mechanically connected to self-supporting body 22.Mechanical connection can limit electrode 62 and prop up certainly Relative stream body sealing between support body 22 flows body into self-supporting body 22 to help prevent.
In each example in example described here, rigid member 30 can include one or more elements.For example, exist In example shown in Fig. 9, rigid member 30 includes three substantially coaxial components.Compared with such as one element, use Two or more elements are set for the desired rigidity for realizing rigid member 30 to form rigid member 30 and can provide Meter is freely.
Figure 10 is the functional block diagram of example LPD 12.LPD 12 include processing module 70, memory 72, stimulating module 74, Electrical sensing module 76, communication module 78, sensor 80 and power supply 82.Power supply 82 can include battery, for example, rechargeable or non- Rechargeable battery.
The module being included in LPD 12 represents the function that can be included in the LPD 12 of the disclosure.The module of present disclosure Any discrete and/or integrated electronic circuit part can be included, the part is performed to produce and is attributed to the mould in this The analog circuit and/or digital circuit of the function of block.For example, the module can include analog circuit, for example, amplifying circuit, Filter circuit, and/or other circuit for signal conditioning.The module can also include digital circuit, for example, combinational logic circuit or Sequential logical circuit, memory devices etc..The function of being attributed to the module in this can be embodied as one or many Individual processor, hardware, firmware, software or its any combinations.Different characteristic is depicted as module to be intended to highlight different functions Aspect and do not necessarily imply that this module must be realized by the hardware or software part for separating.Conversely, and one or more The associated function of module can pass through separate hardware or software part perform or be integrated in common or separate hardware or In software part.
Processing module 70 can include microprocessor, controller, digital signal processor (DSP), special IC (ASIC), field programmable gate array (FPGA), or any of equivalent dispersion or integrated logic circuit or many persons.One In a little examples, processing module 70 can include multiple parts, such as one or more microprocessors, one or more controllers, One or more DSP, one or more ASIC or one or more FPGA and other discrete or integrated logic circuits are appointed What combines.
Processing module 70 can be communicated with memory 72.Memory 72 can include computer-readable instruction, described Computer-readable instruction is made processing module 70 perform here and is attributed to the various of processing module 70 when being performed by processing module 70 Function.Memory 72 can include any volatibility, non-volatile, magnetic, or dielectric, such as, random access memory (RAM), read-only storage (ROM), non-volatile ram (NVRAM), electrically erasable ROM (EEPROM), flash memory or appoint What his memory devices.And, memory 72 can include instruction, and the instruction is when executed by one or more processors The module is made to perform the various functions that here is attributed to the module.For example, memory 72 can include pace-making instruction and be worth. The pace-making instruction and value can be updated by programmable device 40 (Fig. 3).
Stimulating module 74 and electrical sensing module 76 are electrically coupled to electrode 20,24.Processing module 70 is configured for control Stimulating module 74 generates electro photoluminescence and via electrode 20,24 to 34 (for example, right ventricle in the example shown in fig. 3 of heart 32) deliver the electro photoluminescence.Electro photoluminescence can include such as pacemaker impulse or any other suitable electro photoluminescence.Processing module 70 Stimulating module 74 can be controlled according to one or more treatment procedures Jing including the pace-making instruction for defining ventricular pacemaking speed Electronic stimulation is delivered by electrode 20,24, the pace-making instruction can be stored in memory 72.
Additionally, processing module 70 be configured for controlling electrical sensing module 76 monitor carry out the signal of self-electrode 20,24 with Just monitor the electrical activity of heart 34.Electrical sensing module 76 can include the circuit for obtaining electric signal.Obtained by electrical sensing module 76 The electric signal for arriving can be including intrinsic cardiac electrical activity, such as intrinsic atrial depolarization and/or intrinsic ventricular depolarization.Inductance Survey module 76 can acquired electric signal is filtered, amplify and be digitized for generate original numerical data.Process Module 70 can receive the digitalized data generated by electrical sensing module 76.In some instances, processing module 70 can be to original Beginning data perform various Digital Signal Processing operations, such as digital filtering.
Processing module 70 can sense cardiac event based on the data received from electrical sensing module 76.For example, process Module 70 can sense atrial electrical activity based on the data received from electrical sensing module 76.For example, in LPD 12 and sensing Extension 14 is implanted in the example in right ventricle 32, and processing module 70 can be based on the data received from electrical sensing module 76 Detection indicates the far field P ripples of atrial impulses event.In some instances, processing module 70 is also based on from electrical sensing module 76 The data for receiving are sensing ventricle electrical activity.For example, processing module 70 can be based on the number received from electrical sensing module 76 According to come detect indicate ventricular sense event R ripples.Both electrode 20 and electrode 24 are used for R ripples and P ripples in processor 70 In sensing both example, processor 70 can detect the R ripples and P ripples from same sensing signal, and sense vector can be with Between electrode 20 and electrode 24.
In some instances, in addition to electrical sensing module 76, LPD 12 includes sensor 80, and which can include various differences At least one of sensor sensor.For example, sensor 80 can be included in pressure sensor and accelerometer at least One.Sensor 80 can generate the signal of at least one of the parameter of instruction patient 12 parameter, such as, but not limited to following At least one every：The activity level of patient 36, hemodynamic pressure and heart sound.
Communication module 78 can be included for being led to another equipment such as programmable device 40 (Fig. 3) or patient monitor Any suitable hardware (for example, antenna), firmware, software or its any combinations believed.Under the control of processing module 70, communication Module 78 can be by means of the antenna being included in communication module 78 from other equipment (such as programmable device 40 or patient monitor) Receive downlink telemetry and up-link remote measurement is sent to the other equipment.
Figure 11 is by the flow chart of the example technique performed without lead pacing system 10.Although Figure 11 be described as it is main by The processing module 70 of LPD 12 is performing, but in other examples, another processor (for example, the processor of programmable device 40) is (single Any part of the technology illustrated in Figure 11 70) can be performed solely or by means of processing module.In addition, although refer to LPD 12 examples being implanted in right ventricle 32 (Fig. 3) are described to the technology, but the technology illustrated in Figure 11 can also be used In other examples.
According to the example illustrated in Figure 11, the control stimulating module 74 of processing module 70 generates pacemaker impulse and via electrode 20th, 24 the pacemaker impulse (90) is delivered to right ventricle 32.For example, electrode 20 can be selected as source electrode, and electrode 24 can be selected as target electrode.Processing module 70 also controls electrical sensing module 76 (Figure 10) using electrode 20,24 to feel Survey electric cardiomotility (92).The electric cardiomotility may, for example, be any combinations of the following：Intrinsic ventricular depolarization, Intrinsic atrial depolarization, other ventricular sense events (for example, pace events), or other atrial impulses events (for example, pace Event).Processing module 70 can receive the electric heart signal for sensing from sensing module 76, and by least detecting far field P Ripple is detecting atrial depolarization.In some instances, processing module 70 control electrical sensing module 76 (Figure 10) in heart 34 not Electric cardiomotility should be sensed using electrode 20,24 during phase.
Technology described in the disclosure (include being attached to image IMD 16, programmable device 24 or various building blocks those Technology) can realize in hardware, software, firmware or its any combinations at least in part.For example, the various aspects of the technology Can realize in one or more processors, including one or more microprocessors, DSP, ASIC, FPGA or any other Equivalent integrated or discrete logic circuit, and any combinations of this base part, the part is in programmable device (such as internal medicine doctor Teacher or patient programmer, stimulator, image processing equipment or other equipment) in be specific.Term " processor " " processes electricity Road " generally may refer to for foregoing logic circuitry in any circuit (individually or with other logic circuits combining) or appoint What his equivalent circuit.
Such hardware, software, firmware can be realized in same equipment or specific installation to support described in the disclosure Various operations and function.Additionally, any one of described unit, module or part may be implemented as it is together or single Solely as discrete but interoperable logical device.As the different characteristic of module or unit description be intended to emphasize it is different Function aspects, and do not necessarily imply that this generic module or unit must be realized by single hardware or software part.Phase Instead, the function being associated with one or more modules or unit can be performed by single hardware or software part, or collection Into in common or single hardware or software part.
When realizing in software, the function of authorizing the system described in the disclosure, equipment and technology can be specific For computer-readable medium (such as RAM, ROM, NVRAM, EEPROM, flash memory, magnetic data storage medium, optical storage of data Medium etc.) on instruction.The instruction can be performed in order to the one or more aspects for supporting the function described in the disclosure.
Have been described with each example.These and other examples are in the scope of the following claims.

Claims (12)

1. a kind of system, including：
It is without lead pacing devices, described to include without lead pacing devices：
Stimulating module, the stimulating module are configured for generating pacemaker impulse；
Sensing module；
Processing module；
Housing, the housing include current-carrying part, wherein, the housing is configured to the within the chamber of the heart for being implanted in patient And the fenced stimulating module, the sensing module and the processing module；And
First electrode, the first electrode are electrically coupled to the sensing module and the stimulating module；And
Sensing extension, the sensing extension extend from the housing, and including：
Self-supporting body, the self-supporting body extend from the housing and including the portions of proximal of bending；And
Second electrode, the second electrode are carried by the self-supporting body and via the current-carrying part electricity of the housing The sensing module and the stimulating module are connected to,
Wherein, the processing module is configured for controlling the sensing module via the second electrode to sense electric heart Activity.
2. the system as claimed in claim 1, further includes the eyelet in the proximal end of the sensing extension.
3. the system as any one of claim 1 to 2, wherein, the second electrode limits and is configured for receiving The blind hole of the eyelet.
4. system as claimed any one in claims 1 to 3, wherein, the current-carrying part of the housing is electrically connected to institute Sensing module is stated, the sensing extension includes the electricity of the current-carrying part that the second electrode is electrically connected to the housing Conductor.
5. the system as any one of Claims 1-4, wherein, the self-supporting body is with about 1.6 newton square The rigidity of rice.
6. the system as any one of claim 1 to 5, wherein, the self-supporting body is with about 0.8 × 10-6Ox Pause square metre (N-m2) to about 4.8 × 10-6N-m2Rigidity.
7. the system as any one of claim 1 to 6, wherein, the self-supporting body is further included：
Electric insulation sleeve pipe；And
Coil type conductor in the electric insulation sheath, the coil type conductor are electrically connected to the second electrode and surround The rigid member coiling.
8. the system as any one of claim 1 to 7, wherein, the rigidity of the self-supporting body is along the self-supporting The length change of body.
9. the system as any one of claim 1 to 8, wherein, the sensing extension is configured so that when described When in the chamber without the implanted heart of lead pacing devices, the second electrode is stayed without lead pacing devices positioned at described Outside the chamber of the heart for staying.
10. system as claimed in any one of claims 1-9 wherein, wherein, the current-carrying part includes the first current-carrying part, institute The second current-carrying part that housing further includes to electrically insulate with first current-carrying part is stated, wherein, the first electrode is by institute State the restriction of the second current-carrying part.
11. systems as any one of claim 1 to 10, further include on the current-carrying part of the housing The electric insulation layer of side, wherein, the electric insulation layer exposes a section of the current-carrying part of the housing, described one section limit with The 3rd electrically common electrode of the second electrode.
12. systems as any one of claim 1 to 11, wherein, the portions of proximal limit of the self-supporting body Determine one of C-shaped, L-shaped or pigtail shape.
CN201580038840.XA 2014-07-17 2015-07-14 Leadless pacing system including sensing extension Active CN106535990B (en)

Applications Claiming Priority (5)

Application Number Priority Date Filing Date Title
US201462025690P 2014-07-17 2014-07-17
US62/025,690 2014-07-17
US14/694,910 US10674928B2 (en) 2014-07-17 2015-04-23 Leadless pacing system including sensing extension
US14/694,910 2015-04-23
PCT/US2015/040394 WO2016011042A1 (en) 2014-07-17 2015-07-14 Leadless pacing system including sensing extension

Publications (2)

Publication Number Publication Date
CN106535990A true CN106535990A (en) 2017-03-22
CN106535990B CN106535990B (en) 2020-03-24

Family

ID=55073532

Family Applications (1)

Application Number Title Priority Date Filing Date
CN201580038840.XA Active CN106535990B (en) 2014-07-17 2015-07-14 Leadless pacing system including sensing extension

Country Status (4)

Country Link
US (3) US10674928B2 (en)
EP (1) EP3194023B1 (en)
CN (1) CN106535990B (en)
WO (1) WO2016011042A1 (en)

Families Citing this family (129)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
ES2661718T3 (en) 2014-01-10 2018-04-03 Cardiac Pacemakers, Inc. Methods and systems to improve communication between medical devices
CN106068141B (en) 2014-01-10 2019-05-14 心脏起搏器股份公司 System and method for detecting cardiac arrhythmia
US10441796B2 (en) 2014-07-17 2019-10-15 Medtronic, Inc. Multi-chamber intracardiac pacing system
US9539423B2 (en) 2014-07-17 2017-01-10 Medtronic, Inc. Interventional medical systems, tools, and methods of use
JP2017525478A (en) 2014-08-22 2017-09-07 カーディアック ペースメイカーズ， インコーポレイテッド Leadless cardiac pacemaker with sensor with low power mode
US10478620B2 (en) 2014-08-26 2019-11-19 Medtronic, Inc. Interventional medical systems, devices, and methods of use
US9675798B2 (en) 2014-08-26 2017-06-13 Medtronic, Inc. Interventional medical systems, devices, and components thereof
CN107073275B (en) 2014-08-28 2020-09-01 心脏起搏器股份公司 Medical device with triggered blanking period
AU2016215745B2 (en) 2015-02-06 2018-03-15 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
CN107206242B (en) 2015-02-06 2020-10-30 心脏起搏器股份公司 Systems and methods for safe delivery of electrical stimulation therapy
US9669230B2 (en) 2015-02-06 2017-06-06 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US10046167B2 (en) 2015-02-09 2018-08-14 Cardiac Pacemakers, Inc. Implantable medical device with radiopaque ID tag
US9789317B2 (en) 2015-02-26 2017-10-17 Medtronic, Inc. Pacing crosstalk detection
EP3265172B1 (en) 2015-03-04 2018-12-19 Cardiac Pacemakers, Inc. Systems for treating cardiac arrhythmias
EP3268083A1 (en) 2015-03-11 2018-01-17 Medtronic Inc. Multi-chamber intracardiac pacing system
WO2016149262A1 (en) 2015-03-18 2016-09-22 Cardiac Pacemakers, Inc. Communications in a medical device system with link quality assessment
US10050700B2 (en) 2015-03-18 2018-08-14 Cardiac Pacemakers, Inc. Communications in a medical device system with temporal optimization
US9687654B2 (en) 2015-04-23 2017-06-27 Medtronic, Inc. System and method for dual-chamber pacing
US9808637B2 (en) 2015-08-11 2017-11-07 Medtronic, Inc. Ventricular tachycardia detection algorithm using only cardiac event intervals
EP3337559B1 (en) 2015-08-20 2019-10-16 Cardiac Pacemakers, Inc. Systems and methods for communication between medical devices
US9853743B2 (en) 2015-08-20 2017-12-26 Cardiac Pacemakers, Inc. Systems and methods for communication between medical devices
US9968787B2 (en) 2015-08-27 2018-05-15 Cardiac Pacemakers, Inc. Spatial configuration of a motion sensor in an implantable medical device
US9956414B2 (en) 2015-08-27 2018-05-01 Cardiac Pacemakers, Inc. Temporal configuration of a motion sensor in an implantable medical device
US10159842B2 (en) 2015-08-28 2018-12-25 Cardiac Pacemakers, Inc. System and method for detecting tamponade
EP3341076B1 (en) 2015-08-28 2022-05-11 Cardiac Pacemakers, Inc. Systems and methods for behaviorally responsive signal detection and therapy delivery
US10226631B2 (en) 2015-08-28 2019-03-12 Cardiac Pacemakers, Inc. Systems and methods for infarct detection
WO2017044389A1 (en) 2015-09-11 2017-03-16 Cardiac Pacemakers, Inc. Arrhythmia detection and confirmation
WO2017062806A1 (en) 2015-10-08 2017-04-13 Cardiac Pacemakers, Inc. Devices and methods for adjusting pacing rates in an implantable medical device
US10258802B2 (en) 2015-11-20 2019-04-16 Cardiac Pacemakers, Inc. Delivery devices and methods for leadless cardiac devices
AU2016355676B2 (en) 2015-11-20 2018-12-13 Cardiac Pacemakers, Inc. Delivery devices and methods for leadless cardiac devices
CN108472490B (en) 2015-12-17 2022-06-28 心脏起搏器股份公司 Conducted communication in a medical device system
US10905886B2 (en) 2015-12-28 2021-02-02 Cardiac Pacemakers, Inc. Implantable medical device for deployment across the atrioventricular septum
US10583303B2 (en) 2016-01-19 2020-03-10 Cardiac Pacemakers, Inc. Devices and methods for wirelessly recharging a rechargeable battery of an implantable medical device
WO2017136548A1 (en) 2016-02-04 2017-08-10 Cardiac Pacemakers, Inc. Delivery system with force sensor for leadless cardiac device
EP3436142A1 (en) 2016-03-31 2019-02-06 Cardiac Pacemakers, Inc. Implantable medical device with rechargeable battery
US10328272B2 (en) 2016-05-10 2019-06-25 Cardiac Pacemakers, Inc. Retrievability for implantable medical devices
US10668294B2 (en) 2016-05-10 2020-06-02 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker configured for over the wire delivery
JP6764956B2 (en) 2016-06-27 2020-10-07 カーディアック ペースメイカーズ， インコーポレイテッド Cardiac therapy system that uses subcutaneously sensed P-waves for resynchronization pacing management
US11207527B2 (en) 2016-07-06 2021-12-28 Cardiac Pacemakers, Inc. Method and system for determining an atrial contraction timing fiducial in a leadless cardiac pacemaker system
US10426962B2 (en) 2016-07-07 2019-10-01 Cardiac Pacemakers, Inc. Leadless pacemaker using pressure measurements for pacing capture verification
US10688304B2 (en) 2016-07-20 2020-06-23 Cardiac Pacemakers, Inc. Method and system for utilizing an atrial contraction timing fiducial in a leadless cardiac pacemaker system
EP3500342B1 (en) 2016-08-19 2020-05-13 Cardiac Pacemakers, Inc. Trans-septal implantable medical device
US10870008B2 (en) 2016-08-24 2020-12-22 Cardiac Pacemakers, Inc. Cardiac resynchronization using fusion promotion for timing management
CN109640809B (en) 2016-08-24 2021-08-17 心脏起搏器股份公司 Integrated multi-device cardiac resynchronization therapy using P-wave to pacing timing
US9955882B2 (en) * 2016-08-31 2018-05-01 Medtronic Xomed, Inc. System to monitor neural integrity
EP3515553B1 (en) 2016-09-21 2020-08-26 Cardiac Pacemakers, Inc. Leadless stimulation device with a housing that houses internal components of the leadless stimulation device and functions as the battery case and a terminal of an internal battery
WO2018057626A1 (en) 2016-09-21 2018-03-29 Cardiac Pacemakers, Inc. Implantable cardiac monitor
US10758737B2 (en) 2016-09-21 2020-09-01 Cardiac Pacemakers, Inc. Using sensor data from an intracardially implanted medical device to influence operation of an extracardially implantable cardioverter
US10449366B2 (en) 2016-09-29 2019-10-22 Medtronic, Inc. Atrial tracking in an intracardiac ventricular pacemaker
US10532212B2 (en) 2016-09-29 2020-01-14 Medtronic, Inc. Atrial tracking in an intracardiac ventricular pacemaker
WO2018081225A1 (en) 2016-10-27 2018-05-03 Cardiac Pacemakers, Inc. Implantable medical device delivery system with integrated sensor
US10413733B2 (en) 2016-10-27 2019-09-17 Cardiac Pacemakers, Inc. Implantable medical device with gyroscope
WO2018081133A1 (en) 2016-10-27 2018-05-03 Cardiac Pacemakers, Inc. Implantable medical device having a sense channel with performance adjustment
US10463305B2 (en) 2016-10-27 2019-11-05 Cardiac Pacemakers, Inc. Multi-device cardiac resynchronization therapy with timing enhancements
US10765871B2 (en) 2016-10-27 2020-09-08 Cardiac Pacemakers, Inc. Implantable medical device with pressure sensor
CN109890457B (en) 2016-10-27 2023-07-04 心脏起搏器股份公司 Use of a separate device for managing pacing pulse energy of a cardiac pacemaker
WO2018081721A1 (en) 2016-10-31 2018-05-03 Cardiac Pacemakers, Inc Systems for activity level pacing
WO2018081713A1 (en) 2016-10-31 2018-05-03 Cardiac Pacemakers, Inc Systems for activity level pacing
US10286214B2 (en) 2016-11-03 2019-05-14 Medtronic, Inc. Atrial tracking in an intracardiac ventricular pacemaker
US10583301B2 (en) 2016-11-08 2020-03-10 Cardiac Pacemakers, Inc. Implantable medical device for atrial deployment
CN109963612B (en) * 2016-11-09 2023-06-16 心脏起搏器股份公司 Cardiac device adaptation curve
CN109952129B (en) 2016-11-09 2024-02-20 心脏起搏器股份公司 System, device and method for setting cardiac pacing pulse parameters for a cardiac pacing device
US11147979B2 (en) 2016-11-21 2021-10-19 Cardiac Pacemakers, Inc. Implantable medical device with a magnetically permeable housing and an inductive coil disposed about the housing
US10639486B2 (en) 2016-11-21 2020-05-05 Cardiac Pacemakers, Inc. Implantable medical device with recharge coil
US10894163B2 (en) 2016-11-21 2021-01-19 Cardiac Pacemakers, Inc. LCP based predictive timing for cardiac resynchronization
EP3541460B1 (en) 2016-11-21 2020-12-23 Cardiac Pacemakers, Inc. Delivery devices and wall apposition sensing
US11198013B2 (en) 2016-11-21 2021-12-14 Cardiac Pacemakers, Inc. Catheter and leadless cardiac devices including electrical pathway barrier
US10881869B2 (en) 2016-11-21 2021-01-05 Cardiac Pacemakers, Inc. Wireless re-charge of an implantable medical device
CN109963618B (en) 2016-11-21 2023-07-04 心脏起搏器股份公司 Leadless cardiac pacemaker with multi-mode communication
US10864377B2 (en) 2016-12-01 2020-12-15 Medtronic, Inc. Pacing mode switching in a ventricular pacemaker
US10207116B2 (en) 2016-12-01 2019-02-19 Medtronic, Inc. Pacing mode switching in a ventricular pacemaker
US10328270B2 (en) 2016-12-13 2019-06-25 Medtronic, Inc. Input switching in a ventricular intracardiac pacemaker
AU2017387024B2 (en) 2016-12-27 2020-04-09 Cardiac Pacemakers, Inc. Leadless delivery catheter with conductive pathway
US10485981B2 (en) 2016-12-27 2019-11-26 Cardiac Pacemakers, Inc. Fixation methods for leadless cardiac devices
EP3562545B1 (en) 2016-12-27 2023-11-08 Cardiac Pacemakers, Inc. Delivery devices and methods for leadless cardiac devices
US10806931B2 (en) 2016-12-27 2020-10-20 Cardiac Pacemakers, Inc. Delivery devices and methods for leadless cardiac devices
US11207532B2 (en) 2017-01-04 2021-12-28 Cardiac Pacemakers, Inc. Dynamic sensing updates using postural input in a multiple device cardiac rhythm management system
EP3573708B1 (en) 2017-01-26 2021-03-10 Cardiac Pacemakers, Inc. Leadless implantable device with detachable fixation
AU2018213326B2 (en) 2017-01-26 2020-09-10 Cardiac Pacemakers, Inc. Intra-body device communication with redundant message transmission
WO2018140623A1 (en) 2017-01-26 2018-08-02 Cardiac Pacemakers, Inc. Leadless device with overmolded components
WO2018140597A2 (en) 2017-01-26 2018-08-02 Cardiac Pacemakers, Inc. Delivery devices and methods for leadless cardiac devices
US11229798B2 (en) 2017-03-10 2022-01-25 Cardiac Pacemakers, Inc. Fixation for leadless cardiac devices
US11160989B2 (en) 2017-03-20 2021-11-02 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
JP6888112B2 (en) 2017-03-20 2021-06-16 カーディアック ペースメイカーズ， インコーポレイテッド Leadless pacing device for treating cardiac arrhythmias
US10994148B2 (en) 2017-03-20 2021-05-04 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
CN110430920B (en) 2017-03-20 2023-10-27 心脏起搏器股份公司 Leadless pacing device for treating cardiac arrhythmias
US10737092B2 (en) 2017-03-30 2020-08-11 Cardiac Pacemakers, Inc. Delivery devices and methods for leadless cardiac devices
EP3606605B1 (en) 2017-04-03 2023-12-20 Cardiac Pacemakers, Inc. Cardiac pacemaker with pacing pulse energy adjustment based on sensed heart rate
US10905872B2 (en) 2017-04-03 2021-02-02 Cardiac Pacemakers, Inc. Implantable medical device with a movable electrode biased toward an extended position
US11577085B2 (en) 2017-08-03 2023-02-14 Cardiac Pacemakers, Inc. Delivery devices and methods for leadless cardiac devices
WO2019036568A1 (en) 2017-08-18 2019-02-21 Cardiac Pacemakers, Inc. Implantable medical device with a flux concentrator and a receiving coil disposed about the flux concentrator
EP3668592B1 (en) 2017-08-18 2021-11-17 Cardiac Pacemakers, Inc. Implantable medical device with pressure sensor
US10758733B2 (en) 2017-09-15 2020-09-01 Medtronic, Inc. Implantable medical device with retractable fixation sheath
US11478653B2 (en) 2017-09-15 2022-10-25 Medtronic, Inc. Electrodes for intra-cardiac pacemaker
WO2019060302A1 (en) 2017-09-20 2019-03-28 Cardiac Pacemakers, Inc. Implantable medical device with multiple modes of operation
US10751542B2 (en) 2017-10-13 2020-08-25 Medtronic, Inc. Power management for implantable medical device systems
US11185703B2 (en) 2017-11-07 2021-11-30 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker for bundle of his pacing
WO2019108482A1 (en) 2017-12-01 2019-06-06 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials and determining a cardiac interval from a ventricularly implanted leadless cardiac pacemaker
WO2019108830A1 (en) 2017-12-01 2019-06-06 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker with reversionary behavior
US11260216B2 (en) 2017-12-01 2022-03-01 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials during ventricular filling from a ventricularly implanted leadless cardiac pacemaker
WO2019108837A1 (en) 2017-12-01 2019-06-06 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials within a search window from a ventricularly implanted leadless cardiac pacemaker
CN111556774A (en) 2017-12-22 2020-08-18 心脏起搏器股份公司 Implantable medical device for vascular deployment
EP3727578B1 (en) 2017-12-22 2022-02-16 Cardiac Pacemakers, Inc. Implantable medical device for vascular deployment
US11529523B2 (en) 2018-01-04 2022-12-20 Cardiac Pacemakers, Inc. Handheld bridge device for providing a communication bridge between an implanted medical device and a smartphone
US10874861B2 (en) 2018-01-04 2020-12-29 Cardiac Pacemakers, Inc. Dual chamber pacing without beat-to-beat communication
US11154706B1 (en) * 2018-01-31 2021-10-26 Newpace Ltd. Pill pacemaker with Bi-V pacing, DDD pacing and AAI with DDD backup pacing
EP3520856B1 (en) * 2018-02-06 2021-11-17 BIOTRONIK SE & Co. KG Intracardiac pacemaker device for vdd or vddr pacing
EP3768160B1 (en) 2018-03-23 2023-06-07 Medtronic, Inc. Vfa cardiac therapy for tachycardia
US11235159B2 (en) 2018-03-23 2022-02-01 Medtronic, Inc. VFA cardiac resynchronization therapy
EP3768369A1 (en) 2018-03-23 2021-01-27 Medtronic, Inc. Av synchronous vfa cardiac therapy
WO2020065582A1 (en) 2018-09-26 2020-04-02 Medtronic, Inc. Capture in ventricle-from-atrium cardiac therapy
US11951313B2 (en) 2018-11-17 2024-04-09 Medtronic, Inc. VFA delivery systems and methods
CN109498983B (en) * 2018-12-29 2024-01-23 创领心律管理医疗器械（上海）有限公司 Leadless pacemaker
US11071872B2 (en) 2019-01-07 2021-07-27 Pacesetter, Inc. Systems and methods for performing pacing using multiple leadless pacemakers
US11097113B2 (en) 2019-01-07 2021-08-24 Pacesetter, Inc. Systems and methods for performing pacing using leadless pacemakers
US11679265B2 (en) 2019-02-14 2023-06-20 Medtronic, Inc. Lead-in-lead systems and methods for cardiac therapy
US11701517B2 (en) 2019-03-11 2023-07-18 Medtronic, Inc. Cardiac resynchronization therapy using accelerometer
WO2020205401A1 (en) 2019-03-29 2020-10-08 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US11697025B2 (en) 2019-03-29 2023-07-11 Medtronic, Inc. Cardiac conduction system capture
EP3946556A1 (en) * 2019-03-29 2022-02-09 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US11213676B2 (en) 2019-04-01 2022-01-04 Medtronic, Inc. Delivery systems for VfA cardiac therapy
US11712188B2 (en) 2019-05-07 2023-08-01 Medtronic, Inc. Posterior left bundle branch engagement
US11305127B2 (en) 2019-08-26 2022-04-19 Medtronic Inc. VfA delivery and implant region detection
WO2021050679A1 (en) 2019-09-11 2021-03-18 Cardiac Pacemakers, Inc. Tools and systems for implanting and/or retrieving a leadless cardiac pacing device with helix fixation
US11571582B2 (en) 2019-09-11 2023-02-07 Cardiac Pacemakers, Inc. Tools and systems for implanting and/or retrieving a leadless cardiac pacing device with helix fixation
US11813466B2 (en) 2020-01-27 2023-11-14 Medtronic, Inc. Atrioventricular nodal stimulation
US20210308472A1 (en) 2020-04-01 2021-10-07 Pacesetter, Inc. Biostimulator having low-polarization electrode(s)
US11911168B2 (en) 2020-04-03 2024-02-27 Medtronic, Inc. Cardiac conduction system therapy benefit determination
US11813464B2 (en) 2020-07-31 2023-11-14 Medtronic, Inc. Cardiac conduction system evaluation

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060241705A1 (en) * 2005-04-22 2006-10-26 Biotronik Crm Patent Ag Cardiac pacemaker
US20130053921A1 (en) * 2011-08-26 2013-02-28 Medtronic, Inc. Holding members for implantable cardiac stimulation devices
US20130116741A1 (en) * 2011-11-04 2013-05-09 Pacesetter, Inc. Dual-chamber leadless intra-cardiac medical device with intra-cardiac extension
CN103381284A (en) * 2005-10-14 2013-11-06 内诺斯蒂姆股份有限公司 Leadless cardiac pacemaker and system
US20130325081A1 (en) * 2012-01-17 2013-12-05 Pacesetter, Inc. Leadless intra-cardiac medical device with dual chamber sensing through electrical and/or mechanical sensing
US20130345770A1 (en) * 2012-06-21 2013-12-26 Pacesetter, Inc. Leadless intra-cardiac medical device with reduced number of feed-thrus
US20140107723A1 (en) * 2012-10-16 2014-04-17 Pacesetter, Inc. Single-chamber leadless intra-cardiac medical device with dual-chamber functionality

Family Cites Families (284)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR1460772A (en) 1965-10-13 1966-01-07 Philips Massiot Mat Medic Pacemaker
FR2044246A5 (en) 1969-05-13 1971-02-19 Philips Massiot Mat Medic
US3659615A (en) 1970-06-08 1972-05-02 Carl C Enger Encapsulated non-permeable piezoelectric powered pacesetter
US3835864A (en) 1970-09-21 1974-09-17 Rasor Ass Inc Intra-cardiac stimulator
USRE30366E (en) 1970-09-21 1980-08-12 Rasor Associates, Inc. Organ stimulator
US3943936A (en) 1970-09-21 1976-03-16 Rasor Associates, Inc. Self powered pacers and stimulators
US4256115A (en) 1976-12-20 1981-03-17 American Technology, Inc. Leadless cardiac pacer
US4157720A (en) 1977-09-16 1979-06-12 Greatbatch W Cardiac pacemaker
US4333469A (en) 1979-07-20 1982-06-08 Telectronics Pty. Ltd. Bone growth stimulator
US5170784A (en) 1990-11-27 1992-12-15 Ceon Ramon Leadless magnetic cardiac pacemaker
US6144879A (en) 1991-05-17 2000-11-07 Gray; Noel Desmond Heart pacemaker
US6044300A (en) 1991-05-17 2000-03-28 Gray; Noel Desmond Heart pacemaker
US5954757A (en) 1991-05-17 1999-09-21 Gray; Noel Desmond Heart pacemaker
US5674259A (en) 1992-10-20 1997-10-07 Gray; Noel Desmond Multi-focal leadless apical cardiac pacemaker
US5243977A (en) 1991-06-26 1993-09-14 Trabucco Hector O Pacemaker
US5312439A (en) 1991-12-12 1994-05-17 Loeb Gerald E Implantable device having an electrolytic storage electrode
US5193539A (en) 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Implantable microstimulator
US5193540A (en) 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
DE69228531T2 (en) 1992-02-20 1999-07-29 Neomedics Inc Implantable bone growth stimulator
JPH05245215A (en) 1992-03-03 1993-09-24 Terumo Corp Heart pace maker
US5404877A (en) 1993-06-04 1995-04-11 Telectronics Pacing Systems, Inc. Leadless implantable sensor assembly and a cardiac emergency warning alarm
US6051017A (en) 1996-02-20 2000-04-18 Advanced Bionics Corporation Implantable microstimulator and systems employing the same
US5895414A (en) 1996-04-19 1999-04-20 Sanchez-Zambrano; Sergio Pacemaker housing
CA2260209C (en) 1996-07-11 2005-08-30 Medtronic, Inc. Minimally invasive implantable device for monitoring physiologic events
DE19638585A1 (en) 1996-09-20 1998-03-26 Biotronik Mess & Therapieg Device for rejection diagnosis after organ transplantation
US5843132A (en) 1996-10-07 1998-12-01 Ilvento; Joseph P. Self-contained, self-powered temporary intravenous pacing catheter assembly
US5814089A (en) 1996-12-18 1998-09-29 Medtronic, Inc. Leadless multisite implantable stimulus and diagnostic system
US6185452B1 (en) 1997-02-26 2001-02-06 Joseph H. Schulman Battery-powered patient implantable device
US6208894B1 (en) 1997-02-26 2001-03-27 Alfred E. Mann Foundation For Scientific Research And Advanced Bionics System of implantable devices for monitoring and/or affecting body parameters
US6164284A (en) 1997-02-26 2000-12-26 Schulman; Joseph H. System of implantable devices for monitoring and/or affecting body parameters
US7114502B2 (en) 1997-02-26 2006-10-03 Alfred E. Mann Foundation For Scientific Research Battery-powered patient implantable device
US6941171B2 (en) 1998-07-06 2005-09-06 Advanced Bionics Corporation Implantable stimulator methods for treatment of incontinence and pain
US6735474B1 (en) 1998-07-06 2004-05-11 Advanced Bionics Corporation Implantable stimulator system and method for treatment of incontinence and pain
US6141588A (en) 1998-07-24 2000-10-31 Intermedics Inc. Cardiac simulation system having multiple stimulators for anti-arrhythmia therapy
US6240316B1 (en) 1998-08-14 2001-05-29 Advanced Bionics Corporation Implantable microstimulation system for treatment of sleep apnea
WO2000040295A1 (en) 1999-01-06 2000-07-13 Ball Semiconductor, Inc. Implantable neuro-stimulator
US7949395B2 (en) 1999-10-01 2011-05-24 Boston Scientific Neuromodulation Corporation Implantable microdevice with extended lead and remote electrode
US6654638B1 (en) 2000-04-06 2003-11-25 Cardiac Pacemakers, Inc. Ultrasonically activated electrodes
US6871099B1 (en) 2000-08-18 2005-03-22 Advanced Bionics Corporation Fully implantable microstimulator for spinal cord stimulation as a therapy for chronic pain
DE60142178D1 (en) 2000-10-11 2010-07-01 Mann Alfred E Found Scient Res IMPROVED ANTENNA FOR AN IMPLANTED MEDICAL MINIATURE DEVICE
US6764446B2 (en) 2000-10-16 2004-07-20 Remon Medical Technologies Ltd Implantable pressure sensors and methods for making and using them
US7024248B2 (en) 2000-10-16 2006-04-04 Remon Medical Technologies Ltd Systems and methods for communicating with implantable devices
US7198603B2 (en) 2003-04-14 2007-04-03 Remon Medical Technologies, Inc. Apparatus and methods using acoustic telemetry for intrabody communications
US7283874B2 (en) 2000-10-16 2007-10-16 Remon Medical Technologies Ltd. Acoustically powered implantable stimulating device
US6628989B1 (en) 2000-10-16 2003-09-30 Remon Medical Technologies, Ltd. Acoustic switch and apparatus and methods for using acoustic switches within a body
US7519421B2 (en) 2001-01-16 2009-04-14 Kenergy, Inc. Vagal nerve stimulation using vascular implanted devices for treatment of atrial fibrillation
US6445953B1 (en) 2001-01-16 2002-09-03 Kenergy, Inc. Wireless cardiac pacing system with vascular electrode-stents
US6788975B1 (en) 2001-01-30 2004-09-07 Advanced Bionics Corporation Fully implantable miniature neurostimulator for stimulation as a therapy for epilepsy
US6735475B1 (en) 2001-01-30 2004-05-11 Advanced Bionics Corporation Fully implantable miniature neurostimulator for stimulation as a therapy for headache and/or facial pain
US7493172B2 (en) 2001-01-30 2009-02-17 Boston Scientific Neuromodulation Corp. Methods and systems for stimulating a nerve originating in an upper cervical spine area to treat a medical condition
US7127286B2 (en) 2001-02-28 2006-10-24 Second Sight Medical Products, Inc. Implantable device using ultra-nanocrystalline diamond
US7167751B1 (en) 2001-03-01 2007-01-23 Advanced Bionics Corporation Method of using a fully implantable miniature neurostimulator for vagus nerve stimulation
US6592518B2 (en) 2001-04-05 2003-07-15 Kenergy, Inc. Cardiac monitoring system and method with multiple implanted transponders
US6733485B1 (en) 2001-05-25 2004-05-11 Advanced Bionics Corporation Microstimulator-based electrochemotherapy methods and systems
US6947782B2 (en) 2001-06-18 2005-09-20 Alfred E. Mann Foundation For Scientific Research Miniature implantable connectors
US6738672B2 (en) 2001-06-18 2004-05-18 The Alfred E. Mann Foundation For Scientific Research Miniature implantable connectors
US7054692B1 (en) 2001-06-22 2006-05-30 Advanced Bionics Corporation Fixation device for implantable microdevices
WO2003033070A1 (en) 2001-10-16 2003-04-24 Case Western Reserve University Neural prosthesis
WO2003063951A1 (en) 2002-01-29 2003-08-07 Advanced Bionics Corporation Lead assembly for implantable microstimulator
US8321036B2 (en) 2002-02-15 2012-11-27 Data Sciences International, Inc. Cardiac rhythm management device
US7236821B2 (en) 2002-02-19 2007-06-26 Cardiac Pacemakers, Inc. Chronically-implanted device for sensing and therapy
US7203548B2 (en) 2002-06-20 2007-04-10 Advanced Bionics Corporation Cavernous nerve stimulation via unidirectional propagation of action potentials
US20040015205A1 (en) 2002-06-20 2004-01-22 Whitehurst Todd K. Implantable microstimulators with programmable multielectrode configuration and uses thereof
US7292890B2 (en) 2002-06-20 2007-11-06 Advanced Bionics Corporation Vagus nerve stimulation via unidirectional propagation of action potentials
US7860570B2 (en) 2002-06-20 2010-12-28 Boston Scientific Neuromodulation Corporation Implantable microstimulators and methods for unidirectional propagation of action potentials
US20040147973A1 (en) 2002-06-27 2004-07-29 Hauser Robert G. Intra cardiac pacer and method
CA2762938C (en) 2002-06-28 2015-05-05 Boston Scientific Neuromodulation Corporation Microstimulator having self-contained power source and bi-directional telemetry system
US7822480B2 (en) 2002-06-28 2010-10-26 Boston Scientific Neuromodulation Corporation Systems and methods for communicating with an implantable stimulator
US7428438B2 (en) 2002-06-28 2008-09-23 Boston Scientific Neuromodulation Corporation Systems and methods for providing power to a battery in an implantable stimulator
WO2004012810A1 (en) 2002-08-05 2004-02-12 Japan As Represented By President Of National Cardiovascular Center Subminiature integrated heart pace maker and dispersed heart pacing system
US7702395B2 (en) 2002-08-19 2010-04-20 Arizona Board Of Regents, A Body Corporate, Acting For And On Behalf Of Arizona State University Neurostimulator
US20050055061A1 (en) 2003-09-08 2005-03-10 Asher Holzer Cardiac implant device
US20040073267A1 (en) 2002-10-09 2004-04-15 Asher Holzer Micro-generator implant
US20050256549A1 (en) 2002-10-09 2005-11-17 Sirius Implantable Systems Ltd. Micro-generator implant
US20040093039A1 (en) 2002-10-25 2004-05-13 Raphael Schumert Gastrointestinal pacemaker
US20040162590A1 (en) 2002-12-19 2004-08-19 Whitehurst Todd K. Fully implantable miniature neurostimulator for intercostal nerve stimulation as a therapy for angina pectoris
US20040122477A1 (en) 2002-12-19 2004-06-24 Whitehurst Todd K. Fully implantable miniature neurostimulator for spinal nerve root stimulation as a therapy for angina and peripheral vascular disease
US20040133242A1 (en) 2003-01-02 2004-07-08 Chapman Fred W. Medical device communication
US7082336B2 (en) 2003-06-04 2006-07-25 Synecor, Llc Implantable intravascular device for defibrillation and/or pacing
US8239045B2 (en) 2003-06-04 2012-08-07 Synecor Llc Device and method for retaining a medical device within a vessel
US7617007B2 (en) 2003-06-04 2009-11-10 Synecor Llc Method and apparatus for retaining medical implants within body vessels
CA2527909A1 (en) 2003-06-04 2005-01-06 Synecor Llc Intravascular electrophysiological system and methods
US7006864B2 (en) 2003-06-17 2006-02-28 Ebr Systems, Inc. Methods and systems for vibrational treatment of cardiac arrhythmias
US7184830B2 (en) 2003-08-18 2007-02-27 Ebr Systems, Inc. Methods and systems for treating arrhythmias using a combination of vibrational and electrical energy
US6917833B2 (en) 2003-09-16 2005-07-12 Kenergy, Inc. Omnidirectional antenna for wireless communication with implanted medical devices
US20050070962A1 (en) 2003-09-30 2005-03-31 Ebr Systems, Inc. Methods and systems for treating heart failure with vibrational energy
US20060074449A1 (en) 2003-11-03 2006-04-06 Stephen Denker Intravascular stimulation system with wireless power supply
US7003350B2 (en) 2003-11-03 2006-02-21 Kenergy, Inc. Intravenous cardiac pacing system with wireless power supply
US7050849B2 (en) 2003-11-06 2006-05-23 Ebr Systems, Inc. Vibrational therapy device used for resynchronization pacing in a treatment for heart failure
US7450998B2 (en) 2003-11-21 2008-11-11 Alfred E. Mann Foundation For Scientific Research Method of placing an implantable device proximate to neural/muscular tissue
JP2007514482A (en) 2003-12-12 2007-06-07 シネコー・エルエルシー Implantable medical device having a preimplantation exoskeleton
US20090198293A1 (en) 2003-12-19 2009-08-06 Lawrence Cauller Microtransponder Array for Implant
CA2553681A1 (en) 2004-02-10 2005-08-25 Synecor, Llc Intravascular delivery system for therapeutic agents
US7720554B2 (en) 2004-03-29 2010-05-18 Evolution Robotics, Inc. Methods and apparatus for position estimation using reflected light sources
WO2005107864A1 (en) 2004-05-04 2005-11-17 University Of Rochester Leadless implantable cardioverter defibrillator
WO2005107852A1 (en) 2004-05-04 2005-11-17 University Of Rochester Leadless implantable intravascular electrophysiologic device for neurologic/cardiovascular sensing and stimulation
US20050267555A1 (en) 2004-05-28 2005-12-01 Marnfeldt Goran N Engagement tool for implantable medical devices
US20070106357A1 (en) 2005-11-04 2007-05-10 Stephen Denker Intravascular Electronics Carrier Electrode for a Transvascular Tissue Stimulation System
US7765001B2 (en) 2005-08-31 2010-07-27 Ebr Systems, Inc. Methods and systems for heart failure prevention and treatments using ultrasound and leadless implantable devices
US7630767B1 (en) 2004-07-14 2009-12-08 Pacesetter, Inc. System and method for communicating information using encoded pacing pulses within an implantable medical system
US7236829B1 (en) 2004-08-30 2007-06-26 Pacesetter, Inc. Implantable leadless cardiac device with flexible flaps for sensing
EP1799101A4 (en) 2004-09-02 2008-11-19 Proteus Biomedical Inc Methods and apparatus for tissue activation and monitoring
US7771838B1 (en) 2004-10-12 2010-08-10 Boston Scientific Neuromodulation Corporation Hermetically bonding ceramic and titanium with a Ti-Pd braze interface
US7200437B1 (en) 2004-10-13 2007-04-03 Pacesetter, Inc. Tissue contact for satellite cardiac pacemaker
US7532933B2 (en) 2004-10-20 2009-05-12 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
WO2006045075A1 (en) 2004-10-20 2006-04-27 Boston Scientific Limited Leadless cardiac stimulation systems
US7650186B2 (en) 2004-10-20 2010-01-19 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
TWI251986B (en) 2004-10-21 2006-03-21 Univ Nat Sun Yat Sen A wireless transmission system for implantable micro-electrical stimulations system
TWI252007B (en) 2004-10-21 2006-03-21 Univ Nat Sun Yat Sen Communication protocol for implantable micro-electrical stimulations system
US8818504B2 (en) 2004-12-16 2014-08-26 Cardiac Pacemakers Inc Leadless cardiac stimulation device employing distributed logic
EP1833553B1 (en) 2004-12-21 2015-11-18 EBR Systems, Inc. Implantable transducer devices
US7558631B2 (en) 2004-12-21 2009-07-07 Ebr Systems, Inc. Leadless tissue stimulation systems and methods
WO2006069215A2 (en) 2004-12-21 2006-06-29 Ebr Systems, Inc. Leadless cardiac system for pacing and arrhythmia treatment
US7706892B2 (en) 2005-01-20 2010-04-27 Boston Scientific Neuromodulation Corporation Implantable microstimulator with plastic housing and methods of manufacture and use
US7294108B1 (en) 2005-01-27 2007-11-13 Pacesetter, Inc. Cardiac event microrecorder and method for implanting same
EP1843816B1 (en) 2005-02-01 2017-07-12 Second Sight Medical Products, Inc. Micro-miniature implantable coated device
US8165696B2 (en) 2005-02-25 2012-04-24 Boston Scientific Neuromodulation Corporation Multiple-pronged implantable stimulator and methods of making and using such a stimulator
US7532932B2 (en) 2005-03-08 2009-05-12 Kenergy, Inc. Implantable medical apparatus having an omnidirectional antenna for receiving radio frequency signals
US7871415B2 (en) 2005-03-11 2011-01-18 The Johns Hopkins University Devices and methods for treatment of gastrointestinal disorders
US7555345B2 (en) 2005-03-11 2009-06-30 Medtronic, Inc. Implantable neurostimulator device
US7627383B2 (en) 2005-03-15 2009-12-01 Boston Scientific Neuromodulation Corporation Implantable stimulator
US7330756B2 (en) 2005-03-18 2008-02-12 Advanced Bionics Corporation Implantable microstimulator with conductive plastic electrode and methods of manufacture and use
US7363082B2 (en) 2005-03-24 2008-04-22 Synecor Llc Flexible hermetic enclosure for implantable medical devices
US7310556B2 (en) 2005-03-24 2007-12-18 Kenergy, Inc. Implantable medical stimulation apparatus with intra-conductor capacitive energy storage
US7565195B1 (en) 2005-04-11 2009-07-21 Pacesetter, Inc. Failsafe satellite pacemaker system
US7634313B1 (en) 2005-04-11 2009-12-15 Pacesetter, Inc. Failsafe satellite pacemaker system
US7991467B2 (en) 2005-04-26 2011-08-02 Medtronic, Inc. Remotely enabled pacemaker and implantable subcutaneous cardioverter/defibrillator system
US7444180B2 (en) 2005-05-25 2008-10-28 Boston Scientific Neuromodulation Corporation Implantable microstimulator with dissecting tip and/or retrieving anchor and methods of manufacture and use
US7957805B2 (en) 2005-06-01 2011-06-07 Boston Scientific Neuromodulation Corporation Implantable microstimulator with external electrodes disposed on a film substrate and methods of manufacture and use
EP1904173B8 (en) 2005-06-09 2016-06-08 Medtronic, Inc. Implantable medical device with electrodes on multiple housing surfaces
US7295879B2 (en) 2005-06-24 2007-11-13 Kenergy, Inc. Double helical antenna assembly for a wireless intravascular medical device
US8634908B2 (en) 2005-08-01 2014-01-21 Ebr Systems, Inc. Efficiently delivering acoustic stimulation energy to tissue
US7702392B2 (en) 2005-09-12 2010-04-20 Ebr Systems, Inc. Methods and apparatus for determining cardiac stimulation sites using hemodynamic data
US8374696B2 (en) 2005-09-14 2013-02-12 University Of Florida Research Foundation, Inc. Closed-loop micro-control system for predicting and preventing epileptic seizures
US7749265B2 (en) 2005-10-05 2010-07-06 Kenergy, Inc. Radio frequency antenna for a wireless intravascular medical device
US9168383B2 (en) 2005-10-14 2015-10-27 Pacesetter, Inc. Leadless cardiac pacemaker with conducted communication
JP4795772B2 (en) 2005-10-24 2011-10-19 リンテック株式会社 Sheet cutting table and sheet sticking apparatus
US7616990B2 (en) 2005-10-24 2009-11-10 Cardiac Pacemakers, Inc. Implantable and rechargeable neural stimulator
US7917213B2 (en) 2005-11-04 2011-03-29 Kenergy, Inc. MRI compatible implanted electronic medical lead
US8233985B2 (en) 2005-11-04 2012-07-31 Kenergy, Inc. MRI compatible implanted electronic medical device with power and data communication capability
US8255054B2 (en) 2005-11-04 2012-08-28 Kenergy, Inc. MRI compatible implanted electronic medical device
US20070118187A1 (en) 2005-11-21 2007-05-24 Stephen Denker Alerting method for a transvascular tissue stimulation system
WO2007067231A1 (en) 2005-12-09 2007-06-14 Boston Scientific Scimed, Inc. Cardiac stimulation system
US9155479B2 (en) 2005-12-12 2015-10-13 Tor Peters Intra cardiac device, system and methods
JP2009519769A (en) 2005-12-15 2009-05-21 カーディアック ペースメイカーズ， インコーポレイテッド Method and apparatus for small power supplies for implantable devices
US7720547B2 (en) 2006-01-04 2010-05-18 Kenergy, Inc. Extracorporeal power supply with a wireless feedback system for an implanted medical device
EP1971399A1 (en) 2006-01-13 2008-09-24 Universität Duisburg-Essen Stimulation system, in particular a cardiac pacemaker
US7627376B2 (en) 2006-01-30 2009-12-01 Medtronic, Inc. Intravascular medical device
US7519424B2 (en) 2006-01-30 2009-04-14 Medtronic, Inc. Intravascular medical device
US7616992B2 (en) 2006-01-30 2009-11-10 Medtronic, Inc. Intravascular medical device
JP5256048B2 (en) 2006-02-03 2013-08-07 シネコー・エルエルシー Intravascular devices for neuromodulation
US7627371B2 (en) 2006-02-13 2009-12-01 National Sun Yat-Sen University Implantable biomedical chip with modulator for a wireless neural stimulation system
EP1986738B1 (en) 2006-02-24 2010-02-10 Kenergy, Inc. Class-e radio frequency power amplifier with feedback control
KR100895180B1 (en) 2006-04-14 2009-04-24 삼성전자주식회사 Method for Radio Resource Control Connection Setup and Apparatus for the same
US20070276444A1 (en) 2006-05-24 2007-11-29 Daniel Gelbart Self-powered leadless pacemaker
US20070288077A1 (en) 2006-06-07 2007-12-13 Cherik Bulkes Self-anchoring electrical lead with multiple electrodes
US20070288076A1 (en) 2006-06-07 2007-12-13 Cherik Bulkes Biological tissue stimulator with flexible electrode carrier
US7894904B2 (en) 2006-06-20 2011-02-22 Ebr Systems, Inc. Systems and methods for implantable leadless brain stimulation
US7894907B2 (en) 2006-06-20 2011-02-22 Ebr Systems, Inc. Systems and methods for implantable leadless nerve stimulation
US8078283B2 (en) 2006-06-20 2011-12-13 Ebr Systems, Inc. Systems and methods for implantable leadless bone stimulation
US7751881B2 (en) 2006-06-20 2010-07-06 Ebr Systems, Inc. Acoustically-powered wireless defibrillator
US7894910B2 (en) 2006-06-20 2011-02-22 Ebr Systems, Inc. Systems and methods for implantable leadless cochlear stimulation
US7899541B2 (en) 2006-06-20 2011-03-01 Ebr Systems, Inc. Systems and methods for implantable leadless gastrointestinal tissue stimulation
US7899542B2 (en) 2006-06-20 2011-03-01 Ebr Systems, Inc. Systems and methods for implantable leadless spine stimulation
US20070293904A1 (en) 2006-06-20 2007-12-20 Daniel Gelbart Self-powered resonant leadless pacemaker
US7593776B2 (en) 2006-07-05 2009-09-22 University Of Southern California Flexible communication and control protocol for a wireless sensor and microstimulator network
US20080039904A1 (en) 2006-08-08 2008-02-14 Cherik Bulkes Intravascular implant system
WO2008021524A2 (en) 2006-08-18 2008-02-21 Second Sight Medical Products, Inc. Package for an implantable neural stimulation device
US20080077184A1 (en) 2006-09-27 2008-03-27 Stephen Denker Intravascular Stimulation System With Wireless Power Supply
US7979126B2 (en) 2006-10-18 2011-07-12 Boston Scientific Neuromodulation Corporation Orientation-independent implantable pulse generator
US7881803B2 (en) 2006-10-18 2011-02-01 Boston Scientific Neuromodulation Corporation Multi-electrode implantable stimulator device with a single current path decoupling capacitor
US8660660B2 (en) 2006-11-14 2014-02-25 Second Sight Medical Products, Inc. Power scheme for implant stimulators on the human or animal body
US7857819B2 (en) 2006-11-30 2010-12-28 Boston Scientific Neuromodulation Corporation Implant tool for use with a microstimulator
US8311633B2 (en) 2006-12-04 2012-11-13 Synecor Llc Intravascular implantable device having superior anchoring arrangement
AU2008217463B2 (en) 2007-02-16 2013-01-17 Sun Medical-Scientific (Shanghai) Co., Ltd. Non-electrode-lead ultra-thin micro multifunctional heart rate adjusting device
US7640601B2 (en) 2007-03-26 2010-01-05 Moldtek Precision Corp Sports cap
US8103359B2 (en) 2007-05-17 2012-01-24 Cardiac Pacemakers, Inc. Systems and methods for fixating transvenously implanted medical devices
US8718773B2 (en) 2007-05-23 2014-05-06 Ebr Systems, Inc. Optimizing energy transmission in a leadless tissue stimulation system
WO2009006531A1 (en) 2007-07-03 2009-01-08 Ebr Systems, Inc. Minimization of tissue stimulation energy using a microstimulator
JP2010540037A (en) 2007-09-20 2010-12-24 ナノスティム インコーポレイテッド Leadless cardiac pacemaker with secondary fixation capability
US8019419B1 (en) 2007-09-25 2011-09-13 Dorin Panescu Methods and apparatus for leadless, battery-less, wireless stimulation of tissue
US20090082827A1 (en) 2007-09-26 2009-03-26 Cardiac Pacemakers, Inc. Hinged anchors for wireless pacing electrodes
US8412332B2 (en) 2007-10-18 2013-04-02 Integrated Sensing Systems, Inc. Miniature wireless system for deep brain stimulation
CN101185789B (en) 2007-11-06 2010-06-09 浙江大学 Implantation type nerve micro-stimulus and gathering remote-controlled chip
US8060209B2 (en) 2008-01-25 2011-11-15 Boston Scientific Neuromodulation Corporation Methods and systems of treating ischemia pain in visceral organs
CA2711471A1 (en) 2008-01-28 2009-08-06 Boston Scientific Neuromodulation Corporation Fixation of implantable pulse generators
US9005106B2 (en) 2008-01-31 2015-04-14 Enopace Biomedical Ltd Intra-aortic electrical counterpulsation
US8301262B2 (en) 2008-02-06 2012-10-30 Cardiac Pacemakers, Inc. Direct inductive/acoustic converter for implantable medical device
US8588926B2 (en) 2008-03-25 2013-11-19 Ebr Systems, Inc. Implantable wireless accoustic stimulators with high energy conversion efficiencies
US8364276B2 (en) 2008-03-25 2013-01-29 Ebr Systems, Inc. Operation and estimation of output voltage of wireless stimulators
CN101284160A (en) 2008-05-22 2008-10-15 重庆大学 Embedded type device and method for performing magnetic stimulation to nervous tissue by using micro-coil
EP2300792A1 (en) 2008-07-11 2011-03-30 California Institute of Technology Complementary barrier infrared detector
US20110060392A1 (en) 2008-11-13 2011-03-10 Mark Zdeblick Implantable Microstimulators
US8240780B1 (en) 2008-11-26 2012-08-14 Robert Bosch Gmbh Hydraulic brake booster
US20100161002A1 (en) 2008-12-22 2010-06-24 Boston Scientific Neuromodulation Corporation Implantable Medical Device Having A Slot Antenna In Its Case
US8527068B2 (en) 2009-02-02 2013-09-03 Nanostim, Inc. Leadless cardiac pacemaker with secondary fixation capability
US20120045441A1 (en) 2009-03-04 2012-02-23 Sunday Mary E Methods of treating lung disease and other inflammatory diseases
US8886339B2 (en) 2009-06-09 2014-11-11 Setpoint Medical Corporation Nerve cuff with pocket for leadless stimulator
US20100304209A1 (en) 2009-05-29 2010-12-02 Medtronic, Inc. Elongate battery for implantable medical device
US8359098B2 (en) 2009-05-29 2013-01-22 Medtronic, Inc. Implantable medical device with exposed generator
US8541131B2 (en) 2009-05-29 2013-09-24 Medtronic, Inc. Elongate battery for implantable medical device
US9099720B2 (en) 2009-05-29 2015-08-04 Medtronic, Inc. Elongate battery for implantable medical device
US20100305627A1 (en) 2009-05-29 2010-12-02 Medtronic, Inc. Battery with suture hole
US20100305628A1 (en) 2009-05-29 2010-12-02 Medtronic, Inc. Elongate battery for implantable medical device
US8224449B2 (en) 2009-06-29 2012-07-17 Boston Scientific Neuromodulation Corporation Microstimulator with flap electrodes
US20110077708A1 (en) 2009-09-28 2011-03-31 Alan Ostroff MRI Compatible Leadless Cardiac Pacemaker
US8983619B2 (en) 2009-12-30 2015-03-17 Medtronic, Inc. Testing communication during implantation
US8352028B2 (en) 2010-03-26 2013-01-08 Medtronic, Inc. Intravascular medical device
US9421343B2 (en) 2010-04-06 2016-08-23 Medtronic Vascular, Inc. Method of using catheter with rotating portion
US8532790B2 (en) 2010-04-13 2013-09-10 Medtronic, Inc. Slidable fixation device for securing a medical implant
US8478431B2 (en) 2010-04-13 2013-07-02 Medtronic, Inc. Slidable fixation device for securing a medical implant
US20110270340A1 (en) 2010-04-30 2011-11-03 Medtronic Vascular,Inc. Two-Stage Delivery Systems and Methods for Fixing a Leadless Implant to Tissue
US20110270339A1 (en) 2010-04-30 2011-11-03 Medtronic Vascular, Inc. Two-Stage Delivery Systems and Methods for Fixing a Leadless Implant to Tissue
EP2394695B1 (en) 2010-06-14 2012-09-26 Sorin CRM SAS Standalone intracardiac capsule and implantation accessory
US8543190B2 (en) 2010-07-30 2013-09-24 Medtronic, Inc. Inductive coil device on flexible substrate
US8903497B2 (en) 2010-09-30 2014-12-02 Medtronic, Inc. Conformal antenna for implantable medical device and implantable medical device with such antenna
CN103249452A (en) 2010-10-12 2013-08-14 内诺斯蒂姆股份有限公司 Temperature sensor for a leadless cardiac pacemaker
US9060692B2 (en) 2010-10-12 2015-06-23 Pacesetter, Inc. Temperature sensor for a leadless cardiac pacemaker
US20120095539A1 (en) 2010-10-13 2012-04-19 Alexander Khairkhahan Delivery Catheter Systems and Methods
US9020611B2 (en) 2010-10-13 2015-04-28 Pacesetter, Inc. Leadless cardiac pacemaker with anti-unscrewing feature
US20120095521A1 (en) 2010-10-19 2012-04-19 Medtronic, Inc. Detection of heart rhythm using an accelerometer
US9504820B2 (en) 2010-10-29 2016-11-29 Medtronic, Inc. System and method for implantation of an implantable medical device
CN103429296A (en) 2010-12-13 2013-12-04 内诺斯蒂姆股份有限公司 Delivery catheter systems and methods
JP6023720B2 (en) 2010-12-13 2016-11-09 ナノスティム・インコーポレイテッドＮａｎｏｓｔｉｍ， Ｉｎｃ． Pacemaker takeout system and takeout method
US8560892B2 (en) 2010-12-14 2013-10-15 Medtronic, Inc. Memory with selectively writable error correction codes and validity bits
EP2654889B1 (en) 2010-12-20 2017-03-01 Pacesetter, Inc. Leadless pacemaker with radial fixation mechanism
US20120172891A1 (en) 2010-12-29 2012-07-05 Medtronic, Inc. Implantable medical device fixation testing
US9775982B2 (en) 2010-12-29 2017-10-03 Medtronic, Inc. Implantable medical device fixation
US10112045B2 (en) 2010-12-29 2018-10-30 Medtronic, Inc. Implantable medical device fixation
US8386051B2 (en) 2010-12-30 2013-02-26 Medtronic, Inc. Disabling an implantable medical device
US8639335B2 (en) 2011-01-28 2014-01-28 Medtronic, Inc. Disabling an implanted medical device with another medical device
US20130238056A1 (en) 2012-03-06 2013-09-12 Pacesetter, Inc. Rf-powered communication for implantable device
US9220897B2 (en) 2011-04-04 2015-12-29 Micron Devices Llc Implantable lead
US20120323099A1 (en) 2011-04-20 2012-12-20 Medtronic, Inc. Implantable medical device electrode assembly
US8489205B2 (en) 2011-05-03 2013-07-16 Biotronik Se & Co. Kg System for temporary fixation of an implantable medical device
EP2520332A1 (en) 2011-05-05 2012-11-07 Magnetic Pacing Technologies GmbH Implantable stimulation device for defribillation and pacing
EP2704794A4 (en) 2011-05-06 2014-11-05 Ndsu Res Foundation Intelligent self-organizing electrode stimulation delivery system
US20120290021A1 (en) 2011-05-10 2012-11-15 Medtronic, Inc. Battery feedthrough for an implantable medical device
US9592398B2 (en) 2011-05-12 2017-03-14 Medtronic, Inc. Leadless implantable medical device with osmotic pump
EP2537555B1 (en) 2011-06-24 2013-05-01 Sorin CRM SAS Leadless autonomous intracardiac implant with disengageable attachment element
US8968927B2 (en) 2011-07-15 2015-03-03 Covidien Lp Degradable implantable battery
US8989873B2 (en) 2011-07-20 2015-03-24 Medtronic, Inc. Intravascular medical device with advancable electrode
US8478407B2 (en) 2011-07-28 2013-07-02 Medtronic, Inc. Methods for promoting intrinsic activation in single chamber implantable cardiac pacing systems
US8626294B2 (en) 2011-07-29 2014-01-07 Medtronic, Inc. Methods for setting cardiac pacing parameters in relatively high efficiency pacing systems
US8758365B2 (en) 2011-08-03 2014-06-24 Medtronic, Inc. Implant system including guiding accessory and methods of use
US9248300B2 (en) 2011-09-09 2016-02-02 Medtronic, Inc. Controlling wireless communication in an implanted cardiac device
US8945145B2 (en) 2011-09-22 2015-02-03 Medtronic, Inc. Delivery system assemblies for implantable medical devices
US9101281B2 (en) 2011-09-27 2015-08-11 Medtronic, Inc. IMD stability monitor
US8945146B2 (en) 2011-10-24 2015-02-03 Medtronic, Inc. Delivery system assemblies and associated methods for implantable medical devices
US8781605B2 (en) 2011-10-31 2014-07-15 Pacesetter, Inc. Unitary dual-chamber leadless intra-cardiac medical device and method of implanting same
US9017341B2 (en) 2011-10-31 2015-04-28 Pacesetter, Inc. Multi-piece dual-chamber leadless intra-cardiac medical device and method of implanting same
US8798740B2 (en) 2011-11-03 2014-08-05 Pacesetter, Inc. Single chamber leadless intra-cardiac medical device with dual-chamber functionality
US20130123872A1 (en) 2011-11-03 2013-05-16 Pacesetter, Inc. Leadless implantable medical device with dual chamber sensing functionality
US8700181B2 (en) * 2011-11-03 2014-04-15 Pacesetter, Inc. Single-chamber leadless intra-cardiac medical device with dual-chamber functionality and shaped stabilization intra-cardiac extension
US9265436B2 (en) 2011-11-04 2016-02-23 Pacesetter, Inc. Leadless intra-cardiac medical device with built-in telemetry system
WO2013067496A2 (en) 2011-11-04 2013-05-10 Nanostim, Inc. Leadless cardiac pacemaker with integral battery and redundant welds
US20130138006A1 (en) 2011-11-04 2013-05-30 Pacesetter, Inc. Single chamber leadless intra-cardiac medical device having dual chamber sensing with signal discrimination
US9216293B2 (en) 2011-11-17 2015-12-22 Medtronic, Inc. Delivery system assemblies for implantable medical devices
TWI501772B (en) 2011-11-22 2015-10-01 Oneness Biotech Co Plectranthus amboinicus fraction having anti-arthritis activity
WO2013080038A2 (en) 2011-11-28 2013-06-06 Sirius Implantable Systems Ltd. Implantable medical device communications
EP2602001A1 (en) 2011-12-08 2013-06-12 BIOTRONIK SE & Co. KG Medical implant and medical arrangement
US8543204B2 (en) 2011-12-22 2013-09-24 Medtronic, Inc. Timing pacing pulses in single chamber implantable cardiac pacemaker systems
US20130234692A1 (en) 2012-03-07 2013-09-12 Medtronic, Inc. Voltage supply and method with two references having differing accuracy and power consumption
US9607708B2 (en) 2012-03-07 2017-03-28 Medtronic, Inc. Voltage mode sensing for low power flash memory
US10096350B2 (en) 2012-03-07 2018-10-09 Medtronic, Inc. Memory array with flash and random access memory and method therefor, reading data from the flash memory without storing the data in the random access memory
US9053791B2 (en) 2012-03-07 2015-06-09 Medtronic, Inc. Flash memory with integrated ROM memory cells
EP2639845B1 (en) 2012-03-12 2014-11-19 Sorin CRM SAS Autonomous intracorporeal capsule with piezoelectric energy recovery
FR2987747A1 (en) 2012-03-12 2013-09-13 Sorin Crm Sas INTRACORPORAL INDEPENDENT CAPSULE WITH DOUBLE RECOVERY OF ENERGY
US9854982B2 (en) 2012-03-26 2018-01-02 Medtronic, Inc. Implantable medical device deployment within a vessel
US9339197B2 (en) 2012-03-26 2016-05-17 Medtronic, Inc. Intravascular implantable medical device introduction
US10485435B2 (en) 2012-03-26 2019-11-26 Medtronic, Inc. Pass-through implantable medical device delivery catheter with removeable distal tip
US9220906B2 (en) 2012-03-26 2015-12-29 Medtronic, Inc. Tethered implantable medical device deployment
US9717421B2 (en) 2012-03-26 2017-08-01 Medtronic, Inc. Implantable medical device delivery catheter with tether
EP2662113B1 (en) 2012-05-08 2016-08-31 BIOTRONIK SE & Co. KG Leadless heart stimulation and/or monitoring device
US9299962B2 (en) 2012-05-11 2016-03-29 Medtronic, Inc. Battery encasement
TWI475180B (en) 2012-05-31 2015-03-01 Ind Tech Res Inst Synthetic jet equipment
US20130324825A1 (en) 2012-06-05 2013-12-05 Alan Ostroff Leadless Pacemaker with Multiple Electrodes
EP2879758B1 (en) 2012-08-01 2018-04-18 Pacesetter, Inc. Biostimulator circuit with flying cell
US9351648B2 (en) 2012-08-24 2016-05-31 Medtronic, Inc. Implantable medical device electrode assembly
EP2897684B1 (en) 2012-09-20 2017-05-31 Advanced Bionics AG Implantable body with a lead and with engagement wings
US20140100627A1 (en) 2012-10-08 2014-04-10 Pacesetter, Inc. Leadless intra-cardiac medical device with integrated l-c resonant circuit pressure sensor
US8670842B1 (en) 2012-12-14 2014-03-11 Pacesetter, Inc. Intra-cardiac implantable medical device
US20140172034A1 (en) * 2012-12-18 2014-06-19 Pacesetter, Inc. Intra-cardiac implantable medical device with ic device extension for lv pacing/sensing
US8634919B1 (en) 2012-12-20 2014-01-21 Pacesetter, Inc. Intracardiac implantable medical device for biatrial and/or left heart pacing and method of implanting same

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060241705A1 (en) * 2005-04-22 2006-10-26 Biotronik Crm Patent Ag Cardiac pacemaker
CN103381284A (en) * 2005-10-14 2013-11-06 内诺斯蒂姆股份有限公司 Leadless cardiac pacemaker and system
US20130053921A1 (en) * 2011-08-26 2013-02-28 Medtronic, Inc. Holding members for implantable cardiac stimulation devices
US20130116741A1 (en) * 2011-11-04 2013-05-09 Pacesetter, Inc. Dual-chamber leadless intra-cardiac medical device with intra-cardiac extension
US20130325081A1 (en) * 2012-01-17 2013-12-05 Pacesetter, Inc. Leadless intra-cardiac medical device with dual chamber sensing through electrical and/or mechanical sensing
US20130345770A1 (en) * 2012-06-21 2013-12-26 Pacesetter, Inc. Leadless intra-cardiac medical device with reduced number of feed-thrus
US20140107723A1 (en) * 2012-10-16 2014-04-17 Pacesetter, Inc. Single-chamber leadless intra-cardiac medical device with dual-chamber functionality

Also Published As

Publication number Publication date
US10390720B2 (en) 2019-08-27
US20160015287A1 (en) 2016-01-21
EP3194023A1 (en) 2017-07-26
US20200289821A1 (en) 2020-09-17
US10674928B2 (en) 2020-06-09
EP3194023B1 (en) 2024-02-28
WO2016011042A1 (en) 2016-01-21
CN106535990B (en) 2020-03-24
US20160015322A1 (en) 2016-01-21

Similar Documents

Publication Publication Date Title
CN106535990A (en) Leadless pacing system including sensing extension
US10279168B2 (en) Leadless pacing device implantation
US11179568B2 (en) Controlling charge flow in the electrical stimulation of tissue
EP3548140B1 (en) Systems for selecting stimulation parameters for electrical stimulation devices
US9950179B2 (en) Medical devices for trial stimulation
CN106999714A (en) Without the coordination in lead pacing system to ventricular pacemaking
CN107206243A (en) System and method for treating cardiac arrhythmia
CN110198759A (en) Be detachably fixed part without lead implantable device
US9597508B2 (en) Distributed neuro-modulation system with auxiliary stimulation-recording control units
AU2015321473B2 (en) Systems and methods for providing therapy using electrical stimulation to disrupt neuronal activity
AU2021210396A1 (en) Treatment of obstructive sleep apnea (OSA)
CN109952129A (en) The system, apparatus and method of cardiac pacing pulse parameter are set for cardiac pacing device
JP7352305B2 (en) Control system for an implantable stimulator for stimulating the vagus nerve
CN115869537A (en) Template-based electrophysiological signal source determination
Azevedo et al. Novel Method of Protecting and Connecting CMOS Chips Enables Networked Pacing Leads

Legal Events

Date Code Title Description
C06 Publication
PB01 Publication
SE01 Entry into force of request for substantive examination
SE01 Entry into force of request for substantive examination
GR01 Patent grant
GR01 Patent grant